Optical-based sensing devices

ABSTRACT

An optical-based sensor for detecting the presence or amount of an analyte using both indicator and reference channels. The sensor has a sensor body with a source of radiation embedded therein. Radiation emitted by the source interacts with indicator membrane indicator molecules proximate the surface of the body. At least one optical characteristic of these indicator molecules varies with analyte concentration. For example, the level of fluorescence of fluorescent indicator molecules or the amount of light absorbed by light-absorbing indicator molecules can vary as a function of analyte concentration. In addition, radiation emitted by the source also interacts with reference membrane indicator molecules proximate the surface of the body. Radiation (e.g., light) emitted or reflected by these indicator molecules enters and is internally reflected in the sensor body. Photosensitive elements within the sensor body generate both indicator channel and reference channel signals to provide an accurate indication of the concentration of the analyte. Preferred embodiments are totally self-contained and are sized and shaped for use in vivo in a human being. Such embodiments preferably include a power source, e.g. an inductor, which powers the source of radiation using external means, as well as a transmitter, e.g. an inductor, to transmit to external pickup means the signal representing the level of analyte.

The present application is a continuation of U.S. patent applicationSer. No. 10/784,731, filed Feb. 24, 2004, which is a continuation ofU.S. patent application Ser. No. 09/963,798, filed Sep. 27, 2001, nowU.S. Pat. No. 6,711,423, which is a continuation-in-part of U.S. patentapplication Ser. No. 09/383,148, filed Aug. 26, 1999, now U.S. Pat. No.6,330,464 and of U.S. patent application Ser. No. 09/304,831, filed May5, 1999 and of U.S. patent application Ser. No. 09/140,747, filed onAug. 26, 1998, now U.S. Pat. No. 6,304,766 the entire disclosures ofwhich are incorporated herein by reference as if recited herein in full.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The invention relates to electro-optical sensing devices for detectingthe presence or concentration of an analyte in a liquid or gaseousmedium. More particularly, the invention relates to (but is not in allcases necessarily limited to) optical-based sensing devices which arecharacterized by being totally self-contained, with a smooth and roundedoblong, oval, or elliptical shape (e.g., a bean- or pharmaceuticalcapsule-shape) and an extraordinarily compact size which permit thedevice to be implanted in humans for in-situ detection of variousanalytes.

2. Background Art

U.S. Pat. No. 5,517,313, the disclosure of which is incorporated hereinby reference, describes a fluorescence-based sensing device comprisingindicator molecules and a photosensitive element, e.g., a photodetector.Broadly speaking, in the context of the field of the present invention,indicator molecules are molecules one or more optical characteristics ofwhich is or are affected by the local presence of an analyte. In thedevice according to U.S. Pat. No. 5,517,313, a light source, e.g., alight-emitting diode (“LED”), is located at least partially within alayer of material containing fluorescent indicator molecules or,alternatively, at least partially within a wave guide layer such thatradiation (light) emitted by the source strikes and causes the indicatormolecules to fluoresce. A high-pass filter allows fluorescent lightemitted by the indicator molecules to reach the photosensitive element(photodetector) while filtering out scattered light from the lightsource.

The fluorescence of the indicator molecules employed in the devicedescribed in U.S. Pat. No. 5,517,313 is modulated, i.e., attenuated orenhanced, by the local presence of an analyte. For example, theorange-red fluorescence of the complextris(4,7-diphenyl-1,10-phenanthroline)ruthenium(II) perchlorate isquenched by the local presence of oxygen. Therefore, this complex can beused advantageously as the indicator molecule in an oxygen sensor.Indicator molecules whose fluorescence properties are affected byvarious other analytes are known as well.

Furthermore, indicator molecules which absorb light, with the level ofabsorption being affected by the presence or concentration of ananalyte, are also known. See, for example, U.S. Pat. No. 5,512,246, thedisclosure of which is incorporated by reference, which disclosescompositions whose spectral responses are attenuated by the localpresence of polyhydroxyl compounds such as sugars. It is believed,however, that such light-absorbing indicator molecules have not beenused before in a sensor construct like that taught in U.S. Pat. No.5,517,313 or in a sensor construct as taught herein.

In the sensor described in U.S. Pat. No. 5,517,313, the material whichcontains the indicator molecules is permeable to the analyte. Thus, theanalyte can diffuse into the material from the surrounding test medium,thereby affecting the fluorescence of the indicator molecules. The lightsource, indicator molecule-containing matrix material, high-pass filter,and photodetector are configured such that fluorescent light emitted bythe indicator molecules impacts the photodetector such that anelectrical signal is generated that is indicative of the concentrationof the analyte in the surrounding medium.

The sensing device described in U.S. Pat. No. 5,517,313 represents amarked improvement over devices which constitute prior art with respectto U.S. Pat. No. 5,517,313. There has, however, remained a need forsensors that permit the detection of various analytes in an extremelyimportant environment—the human body. Moreover, further refinements havebeen made in the field, which refinements have resulted in smaller andmore efficient devices.

SUMMARY OF THE INVENTION

In general, a sensor according to one aspect of the invention is totallyself-contained, with a source of radiation (e.g., an LED) and aphotosensitive element (e.g., a photodetector) both completely embeddedwithin a light-transmitting sensor body that functions as a wave guide.Indicator molecules are located on the outer surface of the sensor body,e.g., directly coated thereon or immobilized within a polymer matrixlayer. When the radiation source emits radiation, a substantial portionof the radiation is reflected within the sensor body due to internalreflection from the interface of the sensor body and the surroundingmedium (polymer matrix or medium in which the analyte is present). Whenthe radiation impacts the interface of the sensor body and thesurrounding medium, it interacts with the indicator moleculesimmobilized on the surface of the sensor body. Radiation emitted by theindicator molecules (i.e., fluorescent light in the case of fluorescentindicator molecules) or emitted by the source and not absorbed by theindicator molecules (e.g., in the case of light-absorbing indicatormolecules) is reflected throughout the sensor body due to internalreflection. The internally reflected radiation strikes thephotosensitive element such that a signal is generated that isindicative of the presence and/or concentration of the analyte.

A sensor according to this aspect of the invention is constructed withcomponents that permit the source of radiation to be powered either byexternal means, e.g., an electromagnetic wave, ultrasound, or infraredlight, or by wholly internal means, e.g., by using radioluminescence orcomponents such as microbatteries, microgenerators, piezoelectrics, etc.The sensor also has components to transmit a signal indicative of thelevel of internally reflected light or other radiation, from which levelof internally reflected radiation the analyte concentration isdetermined. Such components may be an inductor that is separate from apower-receiving inductor, or the same inductor might be used both toreceive power-generating electromagnetic energy and to transmitinformation-bearing electromagnetic signal waves.

According to another aspect of the invention, a sensor is constructed tofacilitate its use subcutaneously in a living human being. To that end,according to this aspect of the invention, a sensor is approximately thesize and shape of a bean or pharmaceutical cold capsule. Furthermore,the sensor preferably is provided with a sensor/tissue interface layerwhich either prevents the formation of scar tissue or which overcomesthe formation of scar tissue by promoting the ingrowth ofanalyte-carrying vascularization. The shape of a sensor according tothis aspect of the invention has been found in and of itself to providebeneficial optical properties, and therefore such a sensor could beconstructed for applications other than in the human body, i.e., withoutan interface layer and/or with electrical leads extending into and outof the sensor.

A sensor according to another aspect of the invention is constructedwith light-absorbing (or other radiation-absorbing) indicator moleculeswhich absorb the radiation generated by the source. The level ofabsorption varies as a function of the analyte concentration. Bymeasuring the amount of internally reflected radiation, the analyteconcentration can be determined.

A sensor according to another aspect of the invention capitalizes on therelationship between the density of a medium and its refractive index tomeasure analyte concentration. As analyte concentration varies, thedensity of the medium to which the sensor is exposed changes, andtherefore the refractive index of the surrounding medium changes aswell. As the refractive index of the surrounding medium changes, theamount of light that is reflected internally (or, conversely, whichpasses across the sensor/medium interface) also changes, and this changein illumination can be measured by a photosensitive element within thesensor and correlated with the locally surrounding analyteconcentration.

According to a further aspect of the invention, a sensor is providedwhich includes: (a) at least one analyte sensing indicator channel thatoperates as described above; and (b) at least one additional channelthat serves as an optical reference channel. The optical referencechannel preferably: (a) measures one or more optical characteristic(s)of the indicator molecule (i.e., the indicator molecule of the analytesensing indicator channel) which is unaffected or generally unaffectedby the presence or concentration of the analyte; and/or (b) measures theoptical characteristic of a second control indicator molecule which isunaffected or generally unaffected by the presence or concentration ofthe analyte. In the field of the present invention, indicator moleculesthat are unaffected or generally unaffected by the presence orconcentration of analyte are broadly referred to herein as controlindicator molecules.

The optical reference channel can be used, for example, to compensate orcorrect for: changes or drift in the component operation intrinsic tothe sensor make-up; environment conditions external to the sensor; orcombinations thereof. For example, the optical reference channel can beused to compensate or correct for internal variables induced by, amongother things: aging of the sensor's radiation source; changes affectingthe performance or sensitivity of the photosensitive element;deterioration of the indicator molecules; changes in the radiationtransmissivity of the sensor body, of the indicator matrix layer, etc.;changes in other sensor components; etc. In other examples, the opticalreference channel could also be used to compensate or correct forenvironmental factors (e.g., factors external to the sensor) which couldaffect the optical characteristics or apparent optical characteristicsof the indicator molecule irrespective of the presence or concentrationof the analyte. In this regard, exemplary external factors couldinclude, among other things: the temperature level; the pH level; theambient light present; the reflectivity or the turbidity of the mediumthat the sensor is applied in; etc.

The above and other aspects, features and advantages will be furtherappreciated based on the following description in conjunction with theattached drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other aspects of the invention will be apparent from thedetailed description of the invention and the following figures, whichare given by way of example and not limitation, and in which:

FIG. 1 is a schematic, section view of a fluorescence-based sensoraccording to the invention;

FIG. 2 is a schematic diagram of the fluorescence-based sensor shown inFIG. 1 illustrating the wave guide properties of the sensor;

FIG. 3 is a detail view of the circled portion of FIG. 1 demonstratinginternal reflection within the body of the sensor and a preferredconstruction of the sensor/tissue interface layer;

FIG. 4 is schematic diagram, similar to FIG. 2, illustrating reflectionwithin the sensor body by radiation generated by an internal radiationsource and by fluorescent light emitted by external indicator molecules;

FIG. 5 is a schematic diagram demonstrating use of a sensor according tothe invention in a human being;

FIG. 6 is a schematic section view of a radioluminescent light source;

FIGS. 7 a and 7 b are schematic illustrations demonstrating theoperation of a light-absorbing indicator molecule-based sensor accordingto another aspect of the invention;

FIG. 8 is a formula for an embodiment of the matrix layer, wherein thepolymerized macromolecule of the matrix layer contains a pendant aminogroup on about every one of four monomers;

FIG. 9 illustrates a cross-linked and doped segment of the matrix layerin accordance with the present invention;

FIG. 10 depicts a glucose-sensitive, absorbance-modulated indicatormolecule, 2,3′-dihydroxyboron-4-hydroxy-azobenzene (“Boronate Red”) inaccordance with the present invention;

FIG. 11 depicts an additional embodiment of a glucose-sensitive,absorbance-modulated indicator molecule in accordance with the presentinvention;

FIG. 12 depicts a standard Mannich reaction for linking the indicatormolecule and the doped monomer AEMA;

FIGS. 13 a and 13 b are schematic illustrations demonstrating theoperating principle of a refractive index-based sensor according toanother aspect of the invention.

FIG. 14 a is a top view of a sensor according to another embodiment ofthe invention incorporating a reference channel and a normal indicatorchannel;

FIG. 14 b is a side view of the sensor shown in FIG. 14 a;

FIG. 14 c is a partial side view of modified sensor similar to thatshown in FIG. 14 a including a reference channel and an indicatorchannel;

FIG. 14 d is a perspective view of another embodiment of the inventionincorporating a reference channel and an indicator channel similar tothat shown in FIG. 14 c;

FIG. 14 e is a cross-sectional view taken in the direction of the arrowsA-A shown in FIG. 14 d with the device shown within an external object;

FIG. 14 f is a cross-sectional view taken in the direction of the arrowsB-B shown in FIG. 14 d with the device shown within an external object;

FIG. 15 a is a top view of a sensor according to yet another embodimentof the invention incorporating a reference channel and an indicatorchannel;

FIG. 15 b is a side view of the sensor shown in FIG. 15 a.

FIG. 15 c is a side view of modified sensor similar to that shown inFIG. 15 a including a reference channel and an indicator channel;

FIG. 16 a is a top view of a sensor according to yet another embodimentof the invention incorporating a reference channel and an indicatorchannel;

FIG. 16 b is a side view of the sensor shown in FIG. 16 a;

FIG. 17 a is a side view of a sensor according to yet another embodimentof the invention incorporating a reference channel and an indicatorchannel in a sensor construction having an inner capsule and an outersleeve;

FIG. 17 b is a top view of the sensor shown in FIG. 17 a;

FIG. 17 c is a side view of a sensor according to yet another embodimentof the invention incorporating a reference channel and an indicatorchannel in a sensor construction having an inner capsule and an outersleeve;

FIG. 17 d is a top view of the sensor shown in FIG. 17 c;

FIG. 17 e is a side view of a sensor according to yet another embodimentof the invention incorporating a reference channel and an indicatorchannel in a sensor construction having an inner capsule and an outersleeve;

FIG. 17 f is a top view of the sensor shown in FIG. 17 e;

FIG. 18 a is a side view of a sensor according to an embodiment of theinvention having an inner capsule and an outer sleeve without areference channel;

FIG. 18 b is a top view of the sensor shown in FIG. 18 a;

FIGS. 19 a-19 j show side views of a variety of possible sleeveconstructions demonstrating various pocket arrangements and sleevestructures;

FIGS. 20 a-20 b show a top view and a side view, respectively, ofanother embodiment of the invention including a removable filmcontaining sensing membrane(s); and

FIG. 21 is a graph (provided for illustrative purposes only, reprintedfor convenience from FIG. 10 of U.S. Pat. No. 5,137,833, which isincorporated herein by reference) of light absorption (e.g., opticaldensity) in they axis vs. excitation wavelengths (e.g., emitted from aradiation source) in the x axis, demonstrating an isosbestic point(i.e., a wavelength) at which absorption does not vary based on analyteconcentration.

FIG. 22(A) is a top view of a sensor according to another embodiment ofthe invention having a shielding sleeve (with the shielding sleevepartially removed).

FIG. 22(B) is a cross-sectional side view of the sensor shown in FIG.22(A).

FIG. 22(C) is an enlarged view of a portion of the illustration shown inFIG. 22(B).

FIG. 22(D) is a cross-sectional side view of a sensor according toanother embodiment of the invention.

FIG. 23(A) is a cross-sectional side view of a sensor according toanother embodiment of the invention having an LED radiation source whichemits radiation in two directions.

FIG. 23(B) is an enlarged view of a portion of the illustration shown inFIG. 23(A).

FIG. 23(C) is a cross-sectional side view take along the arrows23(C)-23(C) in FIG. 23(A).

FIG. 23(D) is a schematic side view showing a common LED chip mountedwithin a reflector cup.

FIG. 24(A) is an explanatory graph showing illumination from two sidesof an LED, in accordance with one illustrative example of the embodimentshown in FIG. 23(A).

FIG. 24(B) is an explanatory graph showing illumination from an existingLED mounted on a flat surface.

FIG. 25(A) is a cross-sectional side view of another embodiment of thesensor having radiation emitted from top and bottom sides of a radiationsource (with the sensor membrane omitted).

FIG. 25(B) is a cross-sectional side view of the embodiment shown inFIG. 25(A) with the sensor membrane positioned on the sensor.

FIG. 26 is a cross-sectional side view of another embodiment of thesensor having an optically transparent circuit substrate.

FIG. 27(A) is a cross-sectional side view, taken along the line 27-27 inFIG. 27(B), of another embodiment of the sensor having an internalheating element to inhibit condensation on the sensor.

FIG. 27(B) is a top view of the sensor shown in FIG. 27(A).

FIG. 27(C) is an exploded perspective view showing components of thesensor in FIG. 27(A).

FIGS. 28(A) and 28(B) illustrate actual test data of a step change inthe partial pressure of a gas in one exemplary construction of theembodiment of FIGS. 27(A)-27(C).

FIG. 29(A) illustrates another embodiment of the sensor having a matrixcontaining indicator molecules that possess one or more monomericfunctions and which are copolymerized with one or more hydrophilicmonomers to create a copolymer matrix layer which is suitable for thedetection of analytes in aqueous environments.

FIG. 29(B) is a cross section of the sensor shown in FIG. 29(A).

DETAILED DESCRIPTION OF THE INVENTION Initial Optical-Based SensorEmbodiments

An optical-based sensor (“sensor”) 10 according to one aspect of theinvention, which operates based on the fluorescence of fluorescentindicator molecules, is shown in FIG. 1. The sensor 10 has as itsprimary components a sensor body 12; a matrix layer 14 coated over theexterior surface of the sensor body 12, with fluorescent indicatormolecules 16 distributed throughout the layer; a radiation source 18,e.g. an LED, that emits radiation, including radiation over a range ofwavelengths which interact with the indicator molecules (referred toherein simply as “radiation at a wavelength which interacts with theindicator molecules”), i.e., in the case of a fluorescence-based sensor,a wavelength which causes the indicator molecules 16 to fluoresce; and aphotosensitive element 20, e.g. a photodetector, which, in the case of afluorescence-based sensor, is sensitive to fluorescent light emitted bythe indicator molecules 16 such that a signal is generated in responsethereto that is indicative of the level of fluorescence of the indicatormolecules. In the simplest embodiments, indicator molecules 16 couldsimply be coated on the surface of the sensor body. In preferredembodiments, however, the indicator molecules are contained within thematrix layer 14, which comprises a biocompatible polymer matrix that isprepared according to methods known in the art and coated on the surfaceof the sensor body as explained below. Suitable biocompatible matrixmaterials, which must be permeable to the analyte, include methacrylatesand hydrogels which, advantageously, can be made selectivelypermeable—particularly to the analyte—i.e., they perform a molecularweight cut-off function.

The sensor 12 advantageously is formed from a suitable, opticallytransmissive polymer material which has a refractive index sufficientlydifferent from that of the medium in which the sensor will be used suchthat the polymer will act as an optical wave guide. Preferred materialsare acrylic polymers such as polymethylmethacrylate,polyhydroxypropylmethacrylate and the like, and polycarbonates such asthose sold under the trademark Lexan®. The material allows radiationemployed by the device—radiation generated by the radiation source 18(e.g., light at an appropriate wavelength in embodiments in which theradiation source is an LED) and, in the case of a fluorescence-basedembodiment, fluorescent light emitted by the indicator molecules—totravel through it. As shown in FIG. 2, radiation (e.g., light) isemitted by the radiation source 18 and (at least some) is reflectedinternally at the surface of the sensor body 12, e.g., as at location22, thereby “bouncing” back-and-forth throughout the interior of thesensor body 12.

It has been found that light reflected from the interface of the sensorbody and the surrounding medium is capable of interacting with indicatormolecules coated on the surface (whether coated directly thereon orcontained within a matrix), e.g., exciting fluorescence in fluorescentindicator molecules coated on the surface. In addition, light whichstrikes the interface at angles, measured relative to a normal to theinterface, too small to be reflected passes through the interface andalso excites fluorescence in fluorescent indicator molecules. Othermodes of interaction between the light (or other radiation) and theinterface and the indicator molecules have also been found to be usefuldepending on the construction of and application for the sensor. Suchother modes include evanescent excitation and surface plasmon resonancetype excitation.

As demonstrated by FIGS. 3 and 4, at least some of the light emitted bythe fluorescent indicator molecules 16 enters the sensor body 12, eitherdirectly or after being reflected by the outermost surface (with respectto the sensor body 12) of the matrix layer 14, as illustrated in region30. Such fluorescent light 28 is then reflected internally throughoutthe sensor body 12, much like the radiation emitted by the radiationsource 18 is, and, like the radiation emitted by the radiation source,some will strike the interface between the sensor body and thesurrounding medium at angles too small to be reflected and will passback out of the sensor body. Internal reflection of radiation emitted bythe source 18 and, for fluorescence-based sensors, fluorescent lightemitted by the fluorescent indicator molecules 16, illustratedschematically in FIG. 4, impinges on the photosensitive element 20,which senses the level of such internal illumination.

As further illustrated in FIG. 1, the sensor 10 may also includereflective coatings 32 formed on the ends of the sensor body 12, betweenthe exterior surface of the sensor body and the matrix layer 14, tomaximize or enhance the internal reflection of the radiation and/orlight emitted by fluorescent indicator molecules. The reflectivecoatings may be formed, for example, from paint or from a metallizedmaterial (provided such metallized material does not impede transmissionof telemetry signals to and from the sensor, described below).

As still further illustrated in FIG. 1, an optical filter 34 preferablyis provided on the light-sensitive surface of the photosensitive element(photodetector) 20. This filter, as is known from the prior art,prevents or substantially reduces the amount of radiation generated bythe source 18 from impinging on the photosensitive surface of thephotosensitive element 20. At the same time, the filter allowsfluorescent light emitted by fluorescent indicator molecules to passthrough it to strike the photosensitive region of the detector. Thissignificantly reduces “noise” in the photodetector signal that isattributable to incident radiation from the source 18.

The application for which the sensor 10 according to one aspect of theinvention was developed in particular—although by no means the onlyapplication for which it is suitable—is measuring various biologicalanalytes in the human body, e.g., glucose, oxygen, toxins,pharmaceuticals or other drugs, hormones, and other metabolic analytes.The specific composition of the matrix layer 14 and the indicatormolecules 16 may vary depending on the particular analyte the sensor isto be used to detect and/or where the sensor is to be used to detect theanalyte (i.e., in the blood or in subcutaneous tissues). Two constantrequirements, however, are that the matrix layer 14 facilitate exposureof the indicator molecules to the analyte and that the opticalcharacteristics of the indicator molecules (e.g., the level offluorescence of fluorescent indicator molecules) are a function of theconcentration of the specific analyte to which the indicator moleculesare exposed.

To facilitate use in-situ in the human body, the sensor 10 is formed ina smooth, oblong or rounded shape. Advantageously, it has theapproximate size and shape of a bean or a pharmaceutical gelatincapsule, i.e., it is on the order of approximately 500 microns toapproximately 0.5 inch in length L and on the order of approximately 300microns to approximately 0.3 inch in diameter D, with generally smooth,rounded surfaces throughout. This configuration permits the sensor 10 tobe implanted into the human body, i.e., dermally or into underlyingtissues (including into organs or blood vessels) without the sensorinterfering with essential bodily functions or causing excessive pain ordiscomfort.

Moreover, it will be appreciated that any implant placed within thehuman (or any other animal's) body—even an implant that is comprised of“biocompatible” materials—will cause, to some extent, a “foreign bodyresponse” within the organism into which the implant is inserted, simplyby virtue of the fact that the implant presents a stimulus. In the caseof a sensor 10 that is implanted within the human body, the “foreignbody response” is most often fibrotic encapsulation, i.e., the formationof scar tissue. Glucose—a primary analyte which sensors according to theinvention are expected to be used to detect—may have its rate ofdiffusion or transport hindered by such fibrotic encapsulation. Evenmolecular oxygen (O₂) which is very small, may have its rate ofdiffusion or transport hindered by such fibrotic encapsulation as well.This is simply because the cells forming the fibrotic encapsulation(scar tissue) can be quite dense in nature or have metaboliccharacteristics different from that of normal tissue.

To overcome this potential hindrance to or delay in exposing theindicator molecules to biological analytes, two primary approaches arecontemplated. According to one approach, which is perhaps the simplestapproach, a sensor/tissue interface layer—overlying the surface of thesensor body 12 and/or the indicator molecules themselves when theindicator molecules are immobilized directly on the surface of thesensor body, or overlying the surface of the matrix layer 14 when theindicator molecules are contained therein—is prepared from a materialwhich causes little or acceptable levels of fibrotic encapsulation toform. Two examples of such materials described in the literature ashaving this characteristic are Preclude™ Periocardial Membrane,available from W. L. Gore, and polyisobutylene covalently combined withhydrophiles as described in Kennedy, “Tailoring Polymers for BiologicalUses,” Chemtech, February 1994, pp. 24-31.

Alternatively, a sensor/tissue interface layer that is composed ofseveral layers of specialized biocompatible materials can be providedover the sensor. As shown in FIG. 3, for example, the sensor/tissueinterface layer 36 may include three sublayers 36 a, 36 b, and 36 c. Thesublayer 36 a, a layer which promotes tissue ingrowth, preferably ismade from a biocompatible material that permits the penetration ofcapillaries 37 into it, even as fibrotic cells 39 (scar tissue)accumulate on it. Gore-Tex® Vascular Graft material (ePTFE), Dacron®(PET) Vascular Graft materials which have been in use for many years,and MEDPOR Biomaterial produced from high-density polyethylene(available from POREX Surgical Inc.) are examples of materials whosebasic composition, pore size, and pore architecture promote tissue andvascular ingrowth into the tissue ingrowth layer.

The sublayer 36 b, on the other hand, preferably is a biocompatiblelayer with a pore size (less than 5 micrometers) that is significantlysmaller than the pore size of the tissue ingrowth sublayer 36 a so as toprevent tissue ingrowth. A presently preferred material from which thesublayer 36 b is to be made is the Preclude Periocardial Membrane(formerly called GORE-TEX Surgical Membrane), available from W. L. Gore,Inc., which consists of expanded polytetra-fluoroethylene (ePTFE).

The third sublayer 36 c acts as a molecular sieve, i.e., it provides amolecular weight cut-off function, excluding molecules such asimmunoglobulins, proteins, and glycoproteins while allowing the analyteor analytes of interest to pass through it to the indicator molecules(either coated directly on the sensor body 12 or immobilized within amatrix layer 14). Many well known cellulose-type membranes, e.g., of thesort used in kidney dialysis filtration cartridges, may be used for themolecular weight cut-off layer 36 c.

Although the sensor/tissue interface layer 36 is described and shown inFIG. 3 as including a third, molecular weight cut-off layer 36 c, itwill be appreciated that it is possible to select a polymer from whichto make the matrix layer 14, e.g., a methacrylate or a hydratedhydrophilic acrylic, such that it performs the molecular weight cut-offfunction without the need for a separate sublayer 36 c. It isrecommended, however, that the two sublayers 36 a and 36 b be used, withthe outer layer 36 a promoting tissue ingrowth and the inner layer 36 bpreventing tissue ingrowth, because the inner layer 36 b functions as anadditional barrier (or “prefilter”) between the outer layer 36 a and themolecular weight cut-off layer (whether provided separately or by thematrix layer 14 itself). This reduces the likelihood of the molecularweight cut-off layer becoming clogged or fouled by macromolecules suchas immunoglobulins, extracellular matrix proteins, lipids, and the like,and thereby maximizes the speed and efficiency with which the analyte oranalytes of interest come into contact with the indicator molecules. (Inorder for a sensor to be useful for in vivo testing, the analyteexposure lag time, i.e., the amount of time it takes for theconcentration of analyte to which the indicator molecules are directlyexposed to come to a steady state, must be relatively short, i.e., onthe order of two to five minutes.) Various combinations and permutationsof biocompatible materials from which to construct the sensor/tissueinterface layer will be apparent to those having skill in the medicalimplant art.

Finally, with respect to the sensor/tissue interface layer, in additionto preventing adverse reactions, it is believed that the interface layerenhances reflection of light (whether from fluorescent indicatormolecules or from the radiation source 18) from the outermost surface ofthe matrix layer 14 and into the sensor body 12.

A further aspect of a sensor according to the invention is that it maybe wholly self-contained. In other words, in specific embodiments, thesensor may be constructed in such a way that no electrical leads extendinto or out of the sensor body to supply power to the sensor (e.g., fordriving the source 18) or to transmit signals from the sensor. Rather, asensor according to this aspect of the invention may include a powersource 40 (FIG. 1) that is wholly embedded or encapsulated within thesensor body 12 and a transmitter 42 (FIG. 1) that also is entirelyembedded or encapsulated within the sensor body 12.

(The shape of the sensor 10 has been found in and of itself to providesuperior optical properties, however. Accordingly, embodiments of thesensor having power and/or signal-transmitting leads extending intoand/or out of the sensor body are also within the scope of theinvention.)

In a preferred embodiment, the power source 40 is an inductor, as is thetransmitter 42. Thus, when the sensor is implanted in the body, e.g.between the skin 50 and subcutaneous tissues 52 as shown in FIG. 5, thesensor can be powered—i.e., the radiation source can be caused to emitradiation which interacts with the indicator molecules 16—by exposingthe sensor to a field of electromagnetic radiation 54 created, forexample, by an inductor coil 56 that is housed in an appropriatelyconfigured instrument (not shown) positioned near the sensor. Similarly,the transmitter 42, as an inductor, generates an electromagnetic field58 that is indicative of the level of light striking the photosensitiveelement and hence the presence or concentration of analyte. The field 58constitutes a signal that can be detected by an external receiver 60.The signal may be, for example, a 50 megahertz carrier, amplitudemodulated signal; a frequency modulated signal; a digital signal; or anyother type of electromagnetic wave signal that would be known to onehaving skill in the art.

Alternatively, it is possible to use a single coil and a single inductorfor all telemetry. In such an embodiment, the coil 56 generates theelectromagnetic wave 54 at one frequency to induce a current in theinductor 40, which powers the source of radiation 18; the amount ofinternally reflected light sensed by the photosensitive element 20 istransmitted by the same inductor 40 as a modulated electromagnetic wavewhich induces a current in coil 56. This modulated wave is generated bymodulating the current flowing through inductor 40 by the photosensitiveelement 20 as a function of detected light and is detected by measuringthe resulting induced current in coil 56.

Alternatively, the system could be configured to switch (in rapidsequence) between a power generating mode and a signal transmittingmode. These and other telemetry schemes will be familiar to those havingskill in the art, as such techniques are used relatively commonly, e.g.,in connection with “smart cards” having an implanted integrated circuitchip which can be waved past a sensor to gain access to a building,sometimes referred to as radio frequency identification.

Other contemplated self-contained power sources for driving theradiation source 18 include microbatteries; piezoelectrics (whichgenerate a voltage when exposed to mechanical energy such as ultrasonicsound; micro generators; acoustically (e.g., ultrasound) drivengenerators; and photovoltaic cells, which can be powered by light(infrared) passing through the skin 50.

As yet another alternative, in place of an LED, a radioluminescent lightsource can be used. As illustrated in FIG. 6, such a radioluminescentlight source includes a sealed, optically transmissive vessel 80 (e.g.,cylindrical, spherical, or cubic) with a sample of radioisotope 82, e.g.tritium, contained therein. The radioisotope emits beta particles whichstrike intermediate luminophore molecules 84 coated on the interiorsurface of the vessel 80, thereby causing the intermediate luminophoremolecules to emit light. Although the beta particles are too weak topass through the walls of the vessel, the light emitted by theintermediate luminophore molecules does pass through, therebyilluminating the sensor with light—similarly to an LED—that interactswith the indicator molecules. Such radioluminescent generation of light,and similar generation of light, is known in the art. See, for example,U.S. Pat. No. 4,677,008, the disclosure of which is incorporated byreference, and Chuang and Arnold, “Radioluminescent Light Source forOptical Oxygen Sensors,” 69 Analytical Chemistry No. 10, 1899-1903, May15, 1997, the disclosure of which also is incorporated by reference. Asanother alternative to an LED, the sensor might employ anelectroluminscent lamp such as that shown in U.S. Pat. No. 5,281,825.

With respect to the other components shown in FIG. 1, a temperaturesensor 64 and an optional signal amplifier 66 are also advantageouslyprovided. The temperature sensor 64 measures the locally surroundingtemperature of the ambient tissues and the indicator moleculeenvironment and provides this information to the control logic circuit(not shown). The control logic circuit correlates fluorescence level,for example, with analyte concentration level, thereby correcting theoutput signal for variations affected by temperature. Amplifier 66 is arelatively simple gain circuit which amplifies the signal generated bythe photodetector 20.

To make a sensor according to the invention, the various components andcircuitry of the sensor are assembled onto a precut, 0.2 inch by 0.4inch ceramic (e.g., alumina) substrate 70. The substrate thickness is0.020 inch. All circuit elements are standard surface mount componentsavailable, e.g., from Digi-Key, Garrett, and others. The components areattached to the substrate using standard silver conductive epoxy such asAblebond-84, available from Ablebond.

Next, a high pass filter may be installed on the photosensitive elementby applying a two-part high pass filter epoxy, commonly available fromCVI Laser and others. Thickness of the filter is controlled by precisiondispensing using a Rainin Micropipettor. The high pass filter epoxy iscured in an oven at 125° C. for two hours, as per the manufacturer'sinstructions. Similarly, if desired, a low pass filter may be coatedover the radiation source (LED) by the same method using a commerciallyavailable low pass epoxy formulation. Custom formulations of opticalfilters can be prepared by adding a dye of the desired absorptionspectra into Epotek epoxies. The appropriate concentration of the dopantcan be determined by monitoring wavelength versus transmittance on aUV-Vis scan from a spectrophotometer until the desired spectralproperties are obtained. Such custom-formulated epoxies can be curedsimilarly. Prefabricated glass, polymer, or coated filters may also beused and simply glued to the photosensitive element or devices using anoptically matching adhesive, as is typical.

The circuit board with optical filters (if installed and cured) is thenencapsulated using, e.g., a Lilly No. 4 two-part gelatin capsule as amold. Other gelatin capsules work as well. The long “half” of an emptycapsule is placed upright into a rack. Several drops of optically clearpotting of the appropriate sensor body material, as described above, areadded to fill the capsule to approximately one half of its volume. Thesubstrate with pre-assembled circuitry is inserted end-on into thecapsule and into the optical potting, which wicks around and into thesmall spaces of the circuit board assembly to help exclude air and thusprevent bubbles from subsequently forming in the finished sensor device.Additional optical potting is added using a micropipettor until thelevel reaches the top of the capsule with the capsule standing upright.The partial assembly is then further degassed by placing the capsule(supported by the rack) under a bell jar vacuum and allowing it to standunder vacuum until any bubbles observed within the capsule have escaped.The assembly is removed from the vacuum and “topped off” with additionaloptical potting, allowing surface tension to fill the gelatincapsule-half above its rim and to create a rounded, hemispherical domeshape that is similar to the opposite end.

The capsule is then placed under UV light and cured for several hours,with the curing time depending on the intensity of the UV sourceavailable. Heat cure and catalyst cure may alternatively be used,depending on the potting material. A full strength cure is obtained bysubsequently incubating the post-UV-cure assembly at 60° C. for 12hours, or otherwise as per the manufacturer's instructions.

The gelatin mold is then removed from the sensor body by soaking theencapsulated assembly in water for several hours to dissolve thegelatin. Several water changes and washes over the course of the timeperiod help to remove all of the gelatin from the surface. The capsuleis then air dried (or oven dried at 60° C.) in preparation for coating.

Once the sensor body is completely dried, it is coated with indicatormolecules. The indicator molecules may be immobilized directly on thesurface of the sensor body using techniques known in the art, or theymay be contained within a matrix layer solution that is coated onto thecentral body. (A matrix layer solution containing fluorescent indicatormolecules may be prepared according to methods known in the art; amatrix layer solution containing light-absorbing indicator molecules maybe prepared as described below.) A convenient method for coating thesensor with a matrix layer is to affix a small (e.g., 32 gauge) wire toone end of the encapsulated circuitry to produce a hanger. This can bedone using the same UV-cured optical potting material. Approximately oneto two microliters of optical potting is placed on the end of the handlewire. The encapsulated circuit is placed in front of a UV lamp with theUV lamp turned off. The wire with optical potting on the tip is touchedto the end of the capsule and the lamp is turned on. The small amount ofoptical potting “adhesive” will be cured immediately, thereby attachingthe wire tip to the capsule. The capsule may now be dipped convenientlyinto matrix layer solutions (and separate indicator molecule solutions,as appropriate) and hung by the wire to cure. The wire may be removedsimply by pulling it after the sensor is completely assembled.

Once the indicator molecules are securely bonded to the surface of thesensor body, whether directly thereon or in a matrix layer, thesensor/tissue interface layer is constructed by inserting the sensorbody into a preformed tubular sleeve of the material and sealing eachend using heat or epoxy or, if the desired sensor/tissue interface layermaterial is in sheet form, by rolling the sensor body longitudinally inthe material and sealing the longitudinal seam and end seams using heator epoxy.

Although the embodiment of a sensor 10 according to the invention shownand described so far has a single radiation source 18 (LED) andphotosensitive element 20 (photodetector), thereby permitting detectionof a single analyte, other configurations and components are possible.For example, two or more different types of indicator molecules may beprovided to sense the presence or concentration of two or more analytes,respectively, with two or more photosensitive elements being provided onthe ceramic substrate 70, each with its own respective transmitter 42.Each photosensitive element would have its own filter 34 designed toallow light from the respective indicator molecules to pass through toit. Similarly, a “two-channel” embodiment could be developed to measureanalyte concentration by two different sensing schemes. In one suchembodiment, for example, some of the indicator molecules would befluorescent indicator molecules and the rest of the indicator moleculeswould be radiation-absorbing indicator molecules (as described below).Two separate photosensitive elements would be provided, each with itsown appropriate filter—one to measure fluorescent light emitted by thefluorescent indicator molecules and one to measure radiation generatedby the source and reflected throughout the sensor, with some absorptionby the radiation-absorbing indicator molecules. Additionally, othertypes of photosensitive elements may be used, e.g., photoresistors,phototransistors, photodiodes, photodarlingtons, photovoltaic cells,positive insulating negative photodiodes, large-area photodiodes,avalanche photodiodes, charge coupled devices, etc.

Moreover, although a sensor according to the invention has beendescribed above primarily as functioning based on fluorescence ofindicator molecules, the invention is not so limited. According toanother aspect of the invention, a sensor construct as per the inventionmay operate based on the light-absorbing characteristics oflight-absorbing indicator molecules. A sensor according to this aspectof the invention could use a sensor construct like that shown in U.S.Pat. No. 5,517,313, referenced above; more preferably, it uses a bean-or pharmaceutical gelatin capsule construct as described above.

As illustrated in FIGS. 7 a and 7 b, when a sensor 110 according to thisaspect of the invention is not exposed to any analyte, thelight-absorbing indicator molecules 116 (which preferably areimmobilized in a matrix layer 114) absorb a certain amount of radiation(light) 119 generated by the radiation source, falling within aparticular range of wavelengths and passing out of the sensor body, andnon-absorbed radiation 121 is reflected back into the sensor body. Whenthe sensor 110 is exposed to analyte such that the light-absorbingindicator molecules 116 are exposed to analyte molecules 117, thelight-absorbing properties of the indicator molecules are affected. Forexample, as shown in FIG. 7 b, the light-absorbing capacity of theindicator molecules 116 may decrease such that the intensity of thelight 121 reflected back into the sensor body 12 increases. The level oflight within the sensor body is measured by a photosensitive element(not shown), as described above.

It will be appreciated that a light-absorbing indicator molecule-basedsensor must be calibrated by determining the illumination intensitylevels for various known concentrations of various analytes of interest.Furthermore, because the radiation (light) being measured is theradiation being emitted by the source itself, it will be furtherappreciated that if the radiation source has a very broad emissionprofile and the light-absorbing indicator molecule has a very narrowrange of absorption wavelengths, a high-pass, low-pass, or band-passfilter may be provided over the photosensitive element so as to permitonly this range of radiation wavelengths to be sensed by thephotosensitive element.

Indicator molecules whose light-absorbing properties are affected byvarious analytes are known in the art. (As noted above, however, it isbelieved that such light-absorbing indicator molecules have not beenused in connection with a sensor construct either like that taughtherein or in U.S. Pat. No. 5,517,313.) For example, U.S. Pat. No.5,512,246 discloses light-absorbing indicator molecules whose ability toabsorb light varies as a function of the local concentration of glucose.In particular, as the local concentration of glucose increases, theability of the indicator molecules to absorb light at a wavelength of515 nanometers decreases. Therefore, if such indicator molecules areused in connection with a bean- or cold capsule-shaped sensor constructas disclosed herein, the level of internal illumination by light at thatwavelength will increase. The local glucose concentration level can thenbe determined from the level of illumination at that wavelength.

Light-absorbing indicator molecules which are responsive to otheranalytes are well known in the art, e.g., as exemplified byphenolphthalein, which changes color in response to a change in pH.

As is the case with a fluorescent indicator molecule-based sensor, asensor which utilizes light-absorbing indicator molecules could have theindicator molecules disposed directly on the surface of the sensor body.It is preferred, however, that the indicator molecules be immobilizedwithin a matrix layer 114, as is shown in FIGS. 7 a and 7 b.

The matrix layer 114 may be manufactured by the low densitypolymerization of various organic monomers, includinghydroxethylmethacrylate (HEMA). HEMA is widely available from sourcessuch as PolyScienses in Warrington, Pa. and Sigma in St. Louis, Mo., andmay be polymerized by means of heating or exposing the monomers toultraviolet light, as widely known and understood in the art.

In a preferred embodiment, the light-absorbing indicator molecules 116are immobilized within the matrix layer 114 by reacting the HEMA with adoped monomer, e.g., aminoethylmethacrylate (AEMA). Duringpolymerization, AEMA introduces a pendant amine group into the matrixlayer 114. Monomers other than AEMA also may be used during themanufacture of the matrix layer 114, including aminopropylmethacrylate(APMA) and other commercially available monomers having differentpendant groups and varying carbon chain lengths between the amino groupand the rest of the monomer. In addition to monomers containing primaryamine groups (e.g., AEMA), monomers containing secondary amine groupsalso may be used for forming the matrix layer 114. Alternatively,pendant cross-linker groups other than amine groups also may be used tocovalently link the indicator molecules 116 to the polymer material ofthe matrix layer 114. Examples of alternative pendant cross-linkergroups include sulfhydryl (—SH), carboxyl (COOH), aldehyde (COH),hydroxyl (OH), cyano (CN), ether, and epoxyl groups.

Although a range of doping ratios may be used to immobilize theindicator molecules 116, a doping ratio of about 1:4 to about 1:20 AEMAto HEMA is preferred. The matrix layer 114 is provided so as to havestoichiometrically one pendant amino group for every three HEMA residuesin the overall polymerized macromolecule of the matrix layer 114. Thisis illustrated by the formula in FIG. 8.

The polymer material of the matrix layer 114 may be cross-linked bystandard cross-linking methods known in the art, including in apreferred embodiment a method using as a cross-linker group abifunctional poly(ethylene glycol) (n) dimethacrylate. The cross-linkergroup may be added as per standard practice during the initialformulation of the monomer. This and other cross-linker groups arecommercially available from PolySciences (Warrington, Pa.). Although thevariable (n) may range from 1 to more than 1000, in a preferredembodiment of the invention, n=1000. The variable (n) may vary dependingon the desired density, porosity, and hydrophilic properties of thematrix layer 114.

FIG. 9 illustrates a segment of the matrix layer 114 in accordance witha preferred embodiment of the present invention, which includes apendant amino doped monomer (AEMA), a HEMA backbone, and a bifunctionalcross-linker group.

The matrix layer 114 offers several advantages to the present invention,including allowing access of the analyte (e.g., glucose) to thelight-absorbing indicator molecules 116; immobilizing the indicatormolecules 116 to prevent them from leaching; maintaining the stabilityof the optical system of the invention; minimizing the amount ofnon-specific binding to the porous matrix of molecules other than thedesired analyte; restricting access of molecules larger than the desiredanalyte; and permitting the porous matrix material to support one ormore additional, biocompatible interface layers. The matrix layer 114also is optically compatible with the sensor body 12 and is able totransmit excitation, emission, absorbance, or refractive indexwavelength(s) of the indicator molecules 116.

Various methods for immobilizing the indicator molecules 116 within thematrix layer 114 are described in the literature and may range frommechanical entrapment to covalent immobilization. See, for example, A.P. Turner, Biosensors, pp. 85-99, Oxford Science Publications, 1987.

In a preferred embodiment, the indicator molecule 116 is aglucose-sensitive, absorbance-modulated indicator molecule which may becovalently immobilized within the matrix layer 114. Duringpolymerization, the indicator molecule 116 covalently attaches to thepolymer backbone through a primary amine pendant group, and togetherthey form the matrix layer 114. This form of immobilization is adaptableto various methods using different types of indicator molecules anddifferent pendant groups on the polymer backbone. Examples ofglucose-sensitive, absorbance-modulated indicator molecules include2,3′-dihydroxyboron-4-hydroxy-azobenzene (also known as “Boronate Red”),as depicted in FIG. 10. Glucose can interact with the indicatormolecules 116, as described in U.S. Pat. No. 5,512,246. Anothersimilarly prepared preferred indicator molecule 116 for use in thepresent invention is depicted in FIG. 11.

In a preferred method of immobilizing the indicator molecules 116 shownin FIGS. 10 and 11 in the matrix layer 114, the ortho hydrogen positionof the phenol group (represented by an “*” in the indicator moleculesdepicted in FIGS. 10 and 11) is aminoalkylated using the Mannichreaction, which is known in the organic chemistry art as a reactionwherein certain hydrogens of ketones, esters, phenols, and other organiccompounds may be condensed in the presence of formaldehyde and an amine.The reagents for performing the Mannich reaction are commerciallyavailable from many chemical supply companies, including PierceChemicals. A standard Mannich reaction for linking the indicatormolecule 116 to AEMA is depicted in FIG. 12. By copolymerizing AEMA andHEMA into the polymer backbone of the matrix layer 114, the indicatormolecule 116 can be linked to the polymer material of the matrix layer114 and rendered accessible to the analyte, e.g., glucose.

The indicator molecule 116 may be linked to the polymer material of thematrix layer 114 in various ways, including first coupling the indicatormolecule 116 to AEMA prior to co-polymerization with HEMA.Alternatively, non-covalent, mechanical entrapment of the indicatormolecule 116 may be used by first immobilizing the indicator molecule116 to pendant amine groups of polylysine. The preimmobilizedpolylysine/indicator molecule precursor can then be mixed with HEMAprior to polymerization. Upon polymerization of the methacrylate, thepolylysine/indicator molecule complex is trapped within the methacrylatematrix, while at the same time the indicator molecule 116 remainscovalently immobilized to polylysine.

The sensor 110 otherwise is constructed as described above.

A sensor according to a third aspect of the invention takes advantage ofthe bean- or cold capsule-shaped construct described above (although byno means is limited to such a construct) to facilitate sensing thepresence or concentration of an analyte based on changes in therefractive index of the medium in which the sensor is disposed (or therefractive index of a matrix encapsulating the sensor, if one is used).In general, light traveling through a first medium having a refractiveindex n, will pass across the interface between the first medium and asecond medium having a refractive index n₂ if the angle of incidence ofthe light striking the interface (measured relative to a normal to theinterface) is less than the critical angle θ_(c); light striking theinterface at an angle of incidence greater than the critical angle, onthe other hand, will be reflected internally within the first medium.The critical angle θ_(c)=sin⁻¹(n₂/n₁). Thus, for the limiting case ofn₁>>n₂ such that (n₂/n₁) approaches 0 and the critical angle approaches0°, light will be virtually entirely internally reflected within thefirst medium. Conversely, for the limiting condition of n₁=n₂ such thatthe critical angle=90°, there will be no internal reflection within thefirst medium and all light will pass across the interface into thesecond medium.

This principle is illustrated schematically in FIGS. 13 a and 13 b inthe context of a sensor construct as taught herein. In FIG. 13 a, therefractive index n₁ of the sensor body 12 is substantially larger thanthe refractive index n₂ of the surrounding medium. Therefore, all of theinternal light generated by the source 18—which light, because of thewaveguide properties of the sensor body, will have all possible anglesof incidence from 0° to 90°—striking the interface at angles other thanperfectly perpendicular will be internally reflected within the sensorbody and will be sensed by the photosensitive elements 20. As shown inFIG. 13 b, in contrast, where the refractive index n₂ is equal to therefractive index of the sensor body 12, the critical angle will be 90°(i.e., tangent to the interface between the sensor body and thesurrounding medium), and therefore all light generated by the source 18will pass out of the sensor body 12 and none (or almost none) will besensed by the photosensitive elements 20.

It is possible to capitalize on the relationship between the criticalangle and the relative refractive indices to determine the concentrationof an analyte to which the sensor is exposed because, in general, therefractive index of a medium increases with the density of the medium.For example, if the sensor body is encapsulated in a membrane (notshown) which is selectively permeable (via size exclusion, chargeexclusion, or permselectivity) to the analyte of interest, the densityof the membrane will increase as analyte diffuses into it. This allowsmore light to pass out of the sensor body and causes less light tostrike the photosensitive elements. In other words, with increasinganalyte concentration, the level of internal reflection will decrease,and this decrease can be measured and correlated to the local analyteconcentration.

It should be noted that some biological materials such as proteins,hormones, etc. do not dissolve in water and therefore will not permeatethe membrane. Glucose, salts, and other small molecular weightcompounds, however, are the primary metabolic analytes which willdiffuse into the membrane and therefore are the analytes arefraction-based sensor could be used most effectively to measure.

In the most basic embodiment of a refraction-based sensor, a surroundingmembrane would not need to be used. Such a basic embodiment could beused where the only matter varying in concentration is the analyte ofinterest. For example, as champagne or wine ages, the sugar contentdecreases, as does the density and hence the refractive index of thefluid. Therefore, a sensor according to this aspect of the inventioncould be placed in a bottle of champagne or a cask of wine as it isprocessing and used to measure sugar content as the champagne or winedevelops. Other potential applications are determining the liquid levelinside a vessel or determining the amount of moisture in fuel oil.

Finally, although specific embodiments of the various aspects of theinvention have been described above, it will be appreciated thatnumerous modifications and variations of these embodiments will occur tothose having skill in the art. Such modifications and variations and aredeemed to be within the scope of the following claims.

Additional Embodiments of the Invention

In other embodiments of the invention, a sensor is provided whichincludes: (a) at least one analyte sensing indicator channel thatoperates as described above; and (b) at least one additional channelthat serves as an optical reference channel. The optical referencechannel preferably: (a) measures one or more optical characteristic(s)of the indicator molecule (i.e., the indicator molecule of the analytesensing indicator channel) which is unaffected or generally unaffectedby the presence or concentration of the analyte; and/or (b) measures oneor more optical characteristic(s) of a second control indicator moleculewhich is unaffected or generally unaffected by the presence orconcentration of the analyte. The optical reference channel can operate,for example, generally like the indicator channel. In the presentapplication, indicator molecules that are unaffected or generallyunaffected by the presence or concentration of an analyte are broadlyreferred to herein as control indicator molecules.

The optical reference channel can be used, for example, to compensate orcorrect for: (1) changes or drift in component operations intrinsic tothe sensor make-up; and/or (2) environment conditions external to thesensor. For example, the optical reference channel can be used tocompensate or correct for internal variables induced by, among otherthings: aging of the sensor's radiation source; changes affecting theperformance or sensitivity of a photosensitive element thereof;deterioration or alteration of the indicator molecules; changes in theradiation transmissivity of the sensor body, or of the indicator matrixlayer, etc.; changes in other sensor components; etc. In other examples,the optical reference channel could also be used to compensate orcorrect for environmental factors (e.g., factors external to the sensor)which could affect the optical characteristics or apparent opticalcharacteristics of the indicator molecules irrespective of the presenceor concentration of the analyte. In this regard, exemplary externalfactors could include, among other things: the temperature level; the pHlevel; the ambient light present; the reflectivity or the turbidity ofthe medium that the sensor is applied in; etc.

In the following description, like reference numerals refer to likeparts to that of the previously described embodiments, and allalternatives and variations described herein-above with respect to suchlike parts can also be employed in any of the following embodimentswhere appropriate.

While a variety of methods for obtaining separate indicator channel andreference channel readings can be employed, a number of exemplarymethods are discussed in the following paragraphs. These and othermethods can be employed in any of the sensor embodiments describedherein-below as would be apparent based on this disclosure.

First, an indicator membrane (e.g., such as the membrane 14′ describedbelow) can include indicator molecules that are sensitive to aparticular analyte, such as for instance fluorescent indicator moleculesthat are sensitive to oxygen, and that are contained within a materialthat is permeable to that analyte while a reference membrane (e.g., suchas the membrane 14″ described below) can include the same indicatormolecules within a material that is not permeable-to that analyte. Inthe case of oxygen, for example, the indicator membrane can have anoxygen permeable matrix containing the indicator molecules in such amanner that oxygen freely passes through and contacts the indicatormolecules (in one example, silicon rubber may be employed for theindicator membrane, which is very permeable to oxygen). As a result,fluctuations in values obtained in the reference channel should besubstantially non-attributable to the presence or concentration of theanalyte (e.g., oxygen), but rather to, as described above, for example(1) variables intrinsic to the sensor itself or (2) externalenvironmental factors.

Materials that are substantially impermeable to an analyte (i.e., forthe reference channel) can include, for example: a) materials thatsubstantially prevent penetration of elements (see, as one example, U.S.Pat. No. 3,612,866, discussed below, wherein the reference channel iscoated with varnish); and b) perm-selectable membranes, wherein thecontrol indicator molecules are located within a matrix that isperm-selectable such that it allows certain elements to pass whileblocking certain other elements such as the particular analyte (as oneexample, the matrix can allow negatively charged molecules to pass whileblocking positively charged molecules).

Second, the indicator membrane can include indicator molecules that aresensitive to a particular analyte, such as for example fluorescentindicator molecules that are sensitive to glucose, and that arecontained within a material that is permeable to that analyte while thereference membrane can also include a material that is permeable to thatanalyte, but which does not include the same indicator molecules, butrather control indicator molecules that are, in essence, substantiallyblind to that analyte. For example, when the analyte is glucose and suchglucose is within a liquid (such as, for example, body fluids likeblood, serum, tissue interstitial fluid, etc., or other fluids), placingthe control indicator molecules within a material that is not permeableto such glucose would likely have the additional affect of blockingother factors such as changes in pH, etc., so that the first exampledescribed above would not be desirable. Accordingly, in this secondbasic method, the analyte is allowed to penetrate, but the controlindicator molecules selected in the reference channel are chosen so asto be substantially blind to that analyte. As a result, fluctuationsmeasured by the reference channel should be substantially unattributableto changes in the presence or concentration of that analyte.

Some illustrative, non-limiting, examples of control indicator moleculesthat are substantially blind to an analyte can be made as follows.First, reference is made to U.S. patent application Ser. No. 09/265,979,filed on Mar. 11, 1999, entitled Detection of Analytes by FluorescentLanthanide Metal Chelate Complexes Containing Substituted Ligands, alsoowned by the present assignee, the entire disclosure of which isincorporated herein by reference (and which is a continuation-in-part ofapplication Ser. No. 09/037,960, filed Mar. 11, 1998, the entiredisclosure of which is also incorporated herein by reference), whichdescribes a recognition element, e.g., boronic acid, HO—B—OH, which isused to facilitate binding onto glucose. It is contemplated that, assome examples, control indicator molecules that are substantially“blind” to glucose, for example, can be made by omitting or alteringsuch recognition element.

In particular, the '960 application describes indicator molecules with afluorescent lanthanide metal chelate complex having the formula:M(-Ch(—R_(X)))_(Y)wherein: M represents a lanthanide metal ion; Ch represents a chelatorcomprising a ligand, preferably an organic ligand which can comprise anyone or more of a β-diketone or a nitrogen analog thereof, a dihydroxy, acarboxyl coordinating heterocycle, an enol, a macrobicyclic cryptand(i.e., a cage-type ligand), a phenylphosphonic acid, or apolyamino-polycarboxylic acid. The organic ligand of Ch can alsocomprise any one or more of a heterocycle of nitrogen, sulfur, andlinked carboxyls. The organic ligand of Ch can further comprise any oneor more of an alkane or alkene group, preferably containing 1 to 10carbon atoms, as well as aromatic, carbocyclic or heterocyclic moieties,including benzyl, napthyl, anthryl, phenanthryl, or tetracyl groups.Furthermore, one or more chelators complexed with M can be the same or amixture of different chelators (so-called “mixed ligand or ternarychelates”). R represents an analyte-specific recognition element, one ormore of which is bound to one or more ligands of the chelate complex,but need not be linked to every ligand of the chelate complex. In apreferred embodiment, R can be a boronate group or a compound containinga boronate group for detecting glucose or other cis-diol compound. Xrepresents the number of recognition elements R bound to each of one ormore chelators. X can be an integer from 0 to 8, and in certainpreferred embodiments of the invention, X=0 to 4 or X=0 to 2.Additionally, the number of recognition elements R bound to each of oneor more chelators may be the same or different, provided that for one ormore chelators, X>0. Y represents the number of chelators complexed withM, and can be an integer from 1 to 4. In certain preferred embodimentsof the invention, Y=1, Y=3 or Y=4. Accordingly, in these illustrativecases, in order to make control indicator molecules that aresubstantially blind to the analyte, the recognition element R can beomitted or altered as described above by those in the art.

Third, another method of obtaining separate indicator channel andreference channel readings involves utilizing an indicator moleculehaving an isosbestic point at a particular wavelength or frequency(e.g., at about 440 nm in the non-limiting example shown forillustrative purposes in FIG. 21). An “isosbestic point” involves apoint (i.e., substantially at a particular wavelength) where theabsorptivity, for example, is the same irrespective of the presence orconcentration of an analyte. That is, where a radiation source emitsradiation, e.g., light, over a range of frequencies, light absorbance atcertain frequencies will vary based on the presence or concentration ofthe analyte, but light absorbance at the isosbestic point will remainsubstantially constant irrespective of such analyte presence orconcentration. Accordingly, in this third example, the indicator andreference channels would include indicator molecules having a specificisosbestic point (e.g., the same indicator molecules can be used in eachchannel). The indicator channel can include a filter (e.g., see filter34 discussed below) over a photosensitive element (e.g., aphoto-detector) 20-1, discussed below, allowing light outside of theisosbestic point to be detected by the photosensitive element (e.g., at,for instance, about 500 nm in FIG. 21). On the other hand, the referencechannel will include a filter (e.g., 34 below) over a photosensitiveelement (e.g., a photo-detector) 20-2, discussed below, allowing lightsubstantially at the isosbestic wavelength to penetrate and be detectedby the photosensitive element 20-2. As a result, any variation detectedin the reference channel should be largely irrespective of analytepresence or concentration and can be used as a reference as discussedherein-above. Other indicator molecules having such an isosbestic pointcan be used based upon the particular application at hand. As just someof many examples, see among many other known sources: (a) M. Uttamial,et al., A Fiber-Optic Carbon Dioxide Sensor for Fermentation Monitoring,BIOTECHNOLOGY, Vol. 19, pp. 597-601 (June 1995) (discussinghydroxypyrenetrisulfonic acid (HPTS) (and also seminaphthorhodafluor(SNARF)) for CO₂ sensing) the entire disclosure of which is incorporatedherein by reference; (b) A. Mills, et al., Flourescence PlasticThin-film Sensor for Carbon Dioxide, ANALYST, Vol. 118, pp.839-843 (July1993)(Department of Chemistry, University College of Swansea, SingletonPark, Swansea UK) (discussing HPTS indicators for CO₂ sensing) theentire disclosure of which is incorporated herein by reference; (c) U.S.Pat. No. 5,137,833 (showing a glucose indicator with an isosbestic pointat about 440 nm, see, e.g., FIG. 10 of the '833 patent reproduced hereinat FIG. 21) the entire disclosure of which is incorporated herein byreference.

When indicator molecules having an isosbestic point are used, while thenumber of radiation sources (e.g., LEDs, for instance) may varydepending on circumstances, it may sometimes be preferable to utilize aplurality of radiation sources (e.g., LEDs) in certain cases. Forinstance, sometimes a radiation source (e.g., an LED) may not providesufficient illumination at wavelengths around the isosbestic point suchthat it may be desirable to include an additional LED to providesufficient illumination at such wavelengths.

The reference channels and the indicator channels of the presentinvention can utilize materials as described herein and as known in theart depending on the particular application at hand.

Several examples of using a reference or control during analytedetection are known in the art. For example, U.S. Pat. No. 3,612,866,the entire disclosure of which is incorporated herein by reference,describes a fluorescent oxygen sensor having a reference channelcontaining the same indicator chemistry as the measuring channel, exceptthat the reference channel is coated with varnish to render itimpermeable to oxygen. U.S. Pat. Nos. 4,861,727 and 5,190,729, theentire disclosures of which are also incorporated herein by reference,describe oxygen sensors employing two different lanthanide-basedindicator chemistries that emit at two different wavelengths, aterbium-based indicator being quenched by oxygen and a europium-basedindicator being largely unaffected by oxygen. U.S. Pat. No. 5,094,959,the entire disclosure of which is also incorporated herein by reference,describes an oxygen sensor in which a single indicator molecule isirradiated at a certain wavelength and the fluorescence emitted by themolecule is measured over two different emission spectra having twodifferent sensitivities to oxygen. Specifically, the emission spectrawhich is less sensitive to oxygen is used as a reference to ratio thetwo emission intensities. U.S. Pat. Nos. 5,462,880 and 5,728,422, theentire disclosures of which are also incorporated herein by reference,describe a radiometric fluorescence oxygen sensing method employing areference molecule that is substantially unaffected by oxygen and has aphotodecomposition rate similar to the indicator molecule. Additionally,Muller, B., et al., ANALYST, Vol. 121, pp. 339-343 (March 1996), theentire disclosure of which is incorporated herein by reference,describes a fluorescence sensor for dissolved CO₂, in which a blue LEDlight source is directed through a fiber optic coupler to an indicatorchannel and to a separate reference photodetector which detects changesin the LED light intensity.

In addition, U.S. Pat. No. 4,580,059, the entire disclosure of which isincorporated herein by reference, describes a fluorescent-based sensorcontaining a reference light measuring cell 33 for measuring changes inthe intensity of the excitation light source—see, e.g., column 10, lines1, et seq. Furthermore, U.S. Pat. No. 4,617,277, the entire disclosureof which is also incorporated herein by reference, describes anabsorbance-based sensor for carbon monoxide, in which a referenceelement 12 reflects light from a source 14 to a reference photocell todetermine when a measuring element 10 needs replacement due toirreversible color change.

While a number of embodiments described herein are discussed inreference to the utilization of fluorescent indicator molecules, itshould be readily understood based on this disclosure that thesedescribed embodiments can be modified to utilize any type of indicatormolecules or combinations thereof depending on the particularcircumstances at hand. For example, the membranes 14′ and 14″ (discussedbelow) can both include light-absorbing indicator molecules, such asthose described herein-above. As another example, in some circumstancesit may also be possible to utilize fluorescent indicator molecules inone of the indicator or reference membranes 14′ or 14″ while usinglight-absorbing indicator molecules in the other of the indicator orreference membranes 14′ or 14″; in most cases, however, the indicatorand reference membranes 14′ and 14″ will both use like indicatormolecules, such as described herein.

In addition to the foregoing, a variety of other control methods couldbe employed. For example, in various other embodiments, the controlchannel could use materials or substances that are completely unrelatedto the indicator molecules in the indicator channel. In that regard, forexample, the substance of the reference membrane could merely havedesirable characteristics with respect to one or more of, as someexamples, reflectivity, temperature, pH, and/or various other factors.Notably, in certain embodiments, the reference membrane could contain nocorresponding “chemistry”, but could, for example, be used to justmonitor reflectivity (this could be used, for example, to evaluate if anLED dimmed or if, for example, the surface of the membrane was affectedin some manner).

It is contemplated that one or more reference channels can beincorporated in any of the embodiments disclosed in this application. Avariety of preferred embodiments of sensors incorporating referenceindicators are discussed herein-below. While some alternatives andvariations in the following embodiments are described below, likereference numerals refer to like parts to the previously describedembodiments, and all alternatives and variations described herein-abovewith respect to such like parts can also be employed in any of thefollowing embodiments where appropriate.

FIGS. 14(A)-14(B) illustrate a first embodiment of a sensor 10incorporating an optical reference channel. As shown, the sensor 10preferably includes: a sensor body 12; an indicator membrane 14′ havingfluorescent indicator molecules distributed throughout the membrane; areference membrane 14″ having fluorescent control indicator moleculesdistributed throughout the membrane; a radiation source 18, such as forexample a single LED similar to that described herein-above; anindicator channel photosensitive element 20-1, made, for example,similar to photosensitive element 20 described herein-above; a similarreference channel photosensitive element 20-2; a circuit substrate 70(shown schematically with exemplary circuit elements 70i mountedthereto); a power source 40, such as for example an inductive power coilas shown; and a transmitter 42 such as for example a transmitter coil asshown. In any of the embodiments described herein, the membranes 14′ and14″ can be made, for example, with materials similar to any of theembodiments of the matrix layer 14 discussed above or can comprise anyother appropriate materials within which the indicator molecules can becontained or upon which the indicator molecules can be coated. Themembranes 14′ and 14″ (and/or the sensor body) can also include, ifdesired, a sensor/tissue interface layer similar to any of theembodiments of the layer 36, as discussed above. This illustratedembodiment can also include a number of additional elements, such as,for example, as shown: a filter 34 (e.g., to exclude a wavelength or aspectrum of wavelengths of light emitted by an LED, such as blue, and toallow passage of a wavelength or a spectrum of wavelengths of lightemitted by the fluorescent material, such as red) ; a baffle 130 (e.g.,to inhibit “cross-talk” of light radiated from the indicator channel andthe reference channel); a mask 35 surrounding the aperture to each ofthe photosensitive elements; and/or a temperature sensor 64 (e.g., asdescribed above).

In operation, the sensor 12 can function similar to that described abovewith reference to the embodiments shown in FIGS. 1-13. However, twoseparate sensory readings are obtained to provide: a) an indicatorreading (via the channel including the indicator membrane 14′ and thephotosensitive element 20-1); and b) a reference reading (via thechannel including the reference membrane 14″ and the photosensitiveelement 20-2). Then, the reference reading can be used, for example, toprovide more accurate sensor readings.

An exemplary operation of the device shown in FIGS. 14(A)-14(B) is asfollows. First, the power source 40 causes the radiation emitter 18,e.g., an LED, to emit radiation. The radiation travels within the sensorand reaches both the indicator membrane 14′ and the reference membrane14″ (as shown generally by arrows). Then, the molecules within theserespective membranes excite, e.g., fluoresce, and light is radiatedtherefrom (as also shown by arrows) and received by the respectivephotosensitive elements 20-1 and 20-2. This operation is essentiallylike that described with reference to embodiments described herein-aboveand is thus not repeated. In order to eliminate or reduce “cross-talk”between light emitted from the membranes 14′ and 14″, a baffle 130 canbe included. The baffle is preferably impervious to radiation that couldaffect the photosensitive elements—e.g., painted black or the like. Inthis manner, for example, a single radiation source, e.g., an LED, canbe used for both of the “channels.”

While the device can be fabricated in a variety of ways by those in theart based on this disclosure, one exemplary method of making the deviceshown in FIGS. 14(A)-14(B) can be as follows. Initially, an aluminaceramic substrate, which can readily be fabricated by a large number ofvendors, can be provided for the circuit substrate 70. In addition,inductors, for example, can be provided as the power source 40 and thetransmitter 42. The inductors and discreet components can beelectrically connected to the substrate, such as using commonlyavailable solder paste or conductive epoxy. In addition, otherelectronic components can be attached thereto using, for example, aconductive epoxy, such as in one preferred example ABLEBOND 84 fromAblestick Electronic Materials. Then, the components can be wire bondedto complete the circuit connections. Silicon photo-diodes, such as forexample part no. 150-20-002 from Advanced Photonics, Inc., arepreferably provided as the photosensitive elements 20-1 and 20-2, andare preferably flip chip mounted using ball bonds and conductive epoxy.In addition, the edges of the photosensitive element apertures in thesubstrate are preferably masked with a black, non-transparent andnon-conductive material, such as, for example, E320 from EpoxyTechnology, Inc. An optical filter material, such as, for example,LP-595 from CVI Laser Corp., is preferably placed in the photo-diodeapertures (e.g., apertures cut within the substrate 70) to attenuatelight from the radiation source and/or to attenuate ambient light. Theradiation source employed can be, for example, an LED that emits lightin the blue or ultra-violet bands. Then, this circuit assembly structureis preferably molded into an optically transparent encapsulant. Theencapsulant can help serve as a waveguide and can also provideenvironmental protection for the circuitry. Then, the indicator andreference sensing membranes can be attached inside pockets in thecapsule (e.g., inside depressions in the periphery of the capsule). Thisattachment can be accomplished, for example, by molding pockets into thecapsule and then placing the sensing membranes therein, or by placingthe indicator membranes into the mold prior to encapsulation so thatpockets are formed around the membranes during encapsulation. As noted,this is just one preferred method of construction and the device can beconstructed in a variety of ways. In addition, while the embodimentsshown herein have only two channels (i.e., an indicator channel and areference channel), other embodiments could contain multiple indicatorand/or multiple reference channels.

It is contemplated that the structure illustrated in FIGS. 14(A)-14(B)can be modified in a variety of ways. For example, as shown in FIG.14(C), the device can be modified so that a circuit board 70 is fixed toa flexible circuit (e.g., a cable) as shown, such as via electricalleads or contacts 71. This allows, for example, circuitry to extend fromthe body of the capsule or the like (only a portion thereof is shown inFIG. 14(C)), such as for example: (a) to transmit power into the sensorfrom an external power source; (b) to transmit signals out of the sensorto an external receiver; and/or (c) for other purposes. As anotherexample, as also shown in FIG. 14(C), the circuitry does not necessarilyneed to be fully encapsulated within the bean. In this regard, forexample, the sensor 10 can include, as shown, an outer cover 3′ and anencapsulating waveguide portion 12′ formed within, for example, theillustrated, cross-hatched, region between the photosensitive elementsand the indicator and reference membranes. Although less preferred, theinterior of the sensor 10 could also include a cavity for the circuitrythat contains a gas such as, for example, air, or even a liquid oranother medium through which light, e.g., photons, of desiredwavelengths can travel. Preferably, a waveguide material is providedthat has a refractive index that matches or is near the refractive indexof the material of the indicator and reference membranes so as to ensuretravel of light from the membranes to the photosensitive element. In oneexemplary, and non-limiting, construction, the waveguide portion 12′ canbe made from a PMMA material (i.e., poly(methyl methacrylate)), thecircuit board 70 can be made with a ceramic material, the referencecoating 14″ can contain Ru (ruthenium) in an epoxy, the indicatorcoating 14′ can contain Ru in silicone, the baffle 130 can be made witha black epoxy material, the radiation source 18 can be an LED, and theouter cover 3′ can be made with a glass material.

FIG. 14(D) is a perspective view of a sensor 10 similar to that shown inFIG. 14(C), with like numerals indicating like parts. FIGS. 14(E) and14(F) show widthwise and lengthwise cross-sections of the embodimentshown in FIG. 14(D) with the device inserted in a medium B (e.g.,liquid, gas, etc.). As shown in FIG. 14(F), the flexible circuit orcable 70′ can be made to extend from an outer surface of the medium B toa remote power-source, receiver or other device (not shown) as discussedabove. As shown in FIGS. 14(E) and 14(F), the sensor body 12 can includean encapsulating waveguide material, such as described above, or anencapsulating waveguide material can be in a region 12′ like that shownin FIG. 14(C), or, although less preferred, another substance can beused as described above.

FIGS. 15(A)-15(B) show an additional embodiment of the invention whichis similar to that shown in FIGS. 14(A)-14(B), wherein the radiationsource 18 is provided as two separate radiation sources, e.g., LEDs,18-1 and 18-2 that are supported on a mount 18 m. As shown, the LED 18-1is directed toward the indicator membrane 14′, while the LED 18-2 isdirected towards the reference membrane 14″. As shown, a baffle 130 isonce again preferably included, in this case between the LEDs. Becausemultiple radiation sources, e.g., LEDs, are used in this embodiment, theradiation sources, e.g., LEDs 18-1 and 18-2, can be the same, e.g., emitthe same light, or can be different depending on circumstances.

In embodiments wherein a plurality of radiation sources, e.g., LEDs, areused, certain considerations are preferably addressed. When oneradiation source, e.g., LED, is used, aging or other factors therein canmore likely equally affect both channels. However, when plural radiationsources are used (e.g., one for each channel), differences in radiationsources can create some discrepancies between channels. Accordingly, insuch cases, it is desirable to: a) take steps to provide similarradiation sources (e.g., LEDs) for each channel; and/or b) to calibratethe radiation sources (e.g., LEDs) to one another. For example, whenLEDs are formed from silicon wafers that are cut into LED chips (e.g.,typically from flat, rectangular wafers having diameters of about 3-8inches that are cut into an array of tiny LED chips), the LEDs arepreferably selected from adjacent LEDs within the rectangular wafer orpreferably from within a small distance from one another in the array(e.g., within about a half an inch, or more preferably within about aquarter of an inch, or more preferably within about an eighth of aninch, or more preferably within about a sixteenth of an inch) to be cutfrom the wafer. In that manner, the qualities of the selected LED chipsshould be more likely analogous to one another. In addition, whereplural chips are used which have disparities between them, preferablynormalizing calibrations between the LED chips are initially conductedunder known test conditions to ascertain any discrepancies. It should beunderstood, as described herein, that in some cases, providing aplurality of radiation sources (e.g., LEDs) can have certainadvantages—as some examples: a) a plurality of sources can facilitateillumination at desired locations; and/or b) a plurality of sources can,in some cases, be toggled back and forth to reduce cross-talk betweenchannels, as discussed below.

The device shown in FIGS. 15(A)-15(B) can be used, for example, in thesame manner as the device shown in FIGS. 14(A)-14(B). In order tofurther reduce “cross-talk” between light emitted from the membranes 14′and 14″, instead of or in addition to a baffle 130, the two radiationsources, e.g., LEDs, 18-1 and 18-2 can also be operated so as toalternate emissions back and forth between the respective LEDs. Forexample, the LED 18-1 can be activated for a fraction of a second, thenthe LED 18-2 can be activated for a fraction of a second, etc., with oneLED remaining off during the short interval that the other is on. Inthat manner, cross-talk can be substantially reduced. In anotheralternative, the device can be adapted to provide a time delay betweenreadings for the indicator channel and the reference channel (e.g., theindicator membrane could have pico-second decay while the referencemembrane could have a nano-second decay, or vise-verse, such thatseparate channel readings can be made due to temporal differences inradiation emissions).

While FIG. 15(B) shows the LEDs with central axes each at angles θ ofabout 25 degrees from the generally horizontal upper surface of thesubstrate 70, these angles can be selected as desired and can vary, asjust some examples, between about 0 to 90 degrees depending oncircumstances. In some preferred embodiments, for example, the angles θare about 60 degrees or less, or alternatively about 45 degrees or less.

It is contemplated that the structure illustrated in FIGS. 15(A)-15(B)can be modified in a variety of ways, similar to the embodiment shown inFIGS. 14(A)-14(B). For example, FIG. 15(C) illustrates thatmodifications like that shown in FIG. 14(C) can also be made, such asby: (a) including a flexible circuit (e.g., a cable) as shown, such asvia electrical leads or contacts 71; (b) providing the sensor 10 witheither a fully encapsulated interior, or with a partially encapsulatedinterior with an encapsulant waveguide portion 12′ formed therein; (c)etc. In one exemplary, and non-limiting, construction, a waveguideportion 12′ can be made from a PMMA encapsulant material, a circuitboard 70 can be made with a ceramic FR4 circuit card, a radiation source18 can include two LEDs, a mount 18 m can be a Cu (copper) LED mount,and an outer cover 3′ can be made with a glass material. In onepreferred embodiment, as shown, a low index layer 12″ is also providedover the filters 34 above the photosensitive elements 20-1 and 20-2.Once again, the device can be constructed in a variety of ways based onthis disclosure and the above is only one of many exemplaryconstructions.

As shown in FIG. 15(B), the indicator membrane 14′ and the referencemembrane 14″ can be formed within a pocket or the like at in the surfaceof the body 12. Alternatively, the membranes 14′ and 14″ could also beformed on the surface of the body 12 and not within a pocket or thelike. The use of a pocket or the like, however, can help protect themembranes 14′ and 14″ in use and/or prevent the membranes from bulgingoutward from the side of the body (e.g., eliminating bulges canfacilitate handling such as, for example, if the sensor is inserted intoa patient via a trocar tube or the like). As described above, the sensor10 can also include a sensor/tissue interface layer 36 thereover orpartially thereover (and/or over the membranes 14′ and 14″) made, forexample, with bio-compatible materials, e.g., such as any materialsdescribed herein.

FIGS. 16(A)-16(B) show an additional embodiment of the invention whichis similar to that shown in FIGS. 15(A)-15(B), wherein the radiationsource 18 is provided as two separate radiation sources, e.g., LEDs,18-1 and 18-2 that are supported on mounts 18 m 1 and 18 m 2 on oppositesides of the circuit board 70, respectively. As shown, the LED 18-1 isdirected toward the indicator membrane 14′, while the LED 18-2 isdirected towards the reference membrane 14″. In this manner, forexample, the circuit board 70 can actually operate as a baffle to reduceor eliminate cross-talk. As with the embodiments shown in FIGS.15(A)-15(C), the angle θ can be selected as desired and is preferablybetween about 0 and 90 degrees—and is in some preferred embodiments lessthan about 45 degrees.

The device shown in FIGS. 16(A)-16(B) can be used, for example, in thesame manner as the device shown in FIGS. 15(A)-15(B). In addition, theembodiment shown in FIGS. 16(A)-16(B) can also be modified in each ofthe same ways as described above with respect to the embodiment shown inFIGS. 15(A)-15(B). As shown, the upper and lower surfaces of thesubstrate 70 also preferably include masked areas 35 as shown. Theradiation sources 18-1 and 18-2 are preferably located within thesemasked regions 35. In the embodiment shown in FIGS. 16(A)-16(B), thephotosensitive elements 20-1 and 20-2 are mounted on the same side ofthe circuit board 70 as the respective membranes 14′ and 14″, while inthe preceding examples, the boards 70 had cut-out regions through whichradiation, e.g., light, passed to the photosensitive elements. Inaddition, in the embodiment shown in FIGS. 16(A)-16(B), a filtermaterial 34 is preferably provided on top of these photosensitiveelements rather than within such cut-outs. It should be understood thatthe various examples herein can be modified depending on circumstancesby those in the art based on this disclosure. As one example, thephotosensitive elements in the preceding embodiments could be mounted onthe top of the boards 70 in a manner like that shown in FIG. 16(B)(e.g.,on one side of the board).

FIGS. 17(A)-17(F) illustrate additional embodiments of multiple channelsensors that are made with: (a) an inner capsule containing thephotosensitive elements, etc.; and (b) an outer sleeve having sensingmembranes.

With reference to FIG. 17(A), a sensor 10 is shown having the electroniccomponents inside a capsule 3″. The capsule is preferably made of glass,but it can be made of any suitable material as described below. Thecapsule can also be made, if desired, from biocompatible materials. Asanother example, a soda lime glass capsule material like that of theElectronic Animal Identification Capsules of Detron-Fearing Company ofSt. Paul, Minn., could be used. Preferably, the capsule is hermeticallysealed. As shown, a sleeve S is preferably located around the exteriorsurface of the glass capsule. The sleeve S preferably contains anindicator membrane 14′ and a reference membrane 14″ (e.g., fluorescentmembranes for sensing, for example, glucose, etc.). The electroniccircuitry can be like that used in any of the embodiments describedherein-above. In a preferred construction, the electronic circuitryincludes: components to facilitate power induction into the device; anexcitation light source for the fluorochrome; means for photo-sensing;and means for signal transduction via radio frequency (RF) or passiveinductive telemetry to an external reader. As with the preferredembodiments described herein-above, in one exemplary construction theentire sensor 10 is configured to be implanted subcutaneously below theskin of a patient. The components to facilitate power induction into thedevice preferably include an inductive coil 40 that generates thevoltage and current necessary to power the circuit from an externalmagnetic field generator. The inductive coil 40 can be mounted, forexample, on an a ceramic circuit board 70 or at the end of the circuitboard (as shown). Alternatively, inductive coils can be utilized inmultiple locations at various orientations in order to be best coupledwith the external magnetic field generator.

The radiation sources, e.g., LEDs, 18-1 and 18-2 are preferably mountedon the substrate 70 appropriately to excite the indicator membranes 14′and 14″ (e.g., fluorochrome areas) with light photons (as shown viaarrows A1). As described herein-above, the light photons preferablyexcite the membranes 14′ and 14″ so as to give off fluorescence (asshown via arrows A2), which is detected by the photosensitive elements20-1 and 20-2, respectively. In addition, other components can includean amplifier IC 70A and various passive components 70B to provideamplification and modulation circuits to transduce the photosensitiveelement intensity onto the telemetry coils.

One preferred method of constructing the device is, for example only, asfollows. First, an electronic circuit is placed inside the glass tube3″, which is initially open on the left end E. Preferably, the glass isa borosilicate glass, such as in one embodiment Type 1 borosilicateglass N51A, made by Kimble Glass. (A wide variety of glasses and othermaterials could be used in other embodiments). After the electroniccircuit is placed inside the glass tube 3″, the interior is partiallyfilled with encapsulant waveguide material 12′ to the level indicated bydashed lines at 12L. As described herein-above, an encapsulant waveguidematerial can help to, for example, optically couple the light A-1 to themembrane surfaces 14′ and 14″ and to optically couple the fluorescentsignals A-2 back to the photosensitive elements 20-1 and 20-2. Anyoptically suitable waveguide materials described herein-above or knownin the art can be used. As above, the encapsulant waveguide materialcould also be applied throughout the entire interior of the glass tube3″, or in less preferred embodiments, the glass tube could be filledentirely with air or another substance as the waveguide. In somepreferred embodiments, the waveguide material can include one or more ofthe following materials: silicone; GE RTV 615; PMMA; or an opticaladhesive, such as NORLAND 63.

The capsule 3″ is then preferably sealed at the end E to enclose thecapsule. Preferably, the capsule is a glass capsule that is flame sealedat the end E to provide a smooth rounded end and to provide a hermeticseal. Preferably, prior to sealing the capsule, the electronic device isprocessed to remove moisture. For example, the device can be baked(e.g., at about 75° C. or greater for about 12 hours) and can be placedin a Nitrogen atmosphere to drive any residual moisture from the deviceand its components. Then, the assembled device can be powered andtested, if desired, to evaluate its operability before proceeding to thenext assembly step—e.g., the step of applying the sensing membranes. Inone exemplary construction, especially for use in-vivo, the length lshown in FIG. 17(A) can be about 10-15 mm long, and more preferablyabout 12.5 mm long, while the width h can be about 2-3 mm wide, and morepreferably about 2.5 mm wide. In other preferred embodiments, the sensorcan be substantially smaller—see, for example, preferred size rangesdescribed herein-above (e.g., approximately 500 microns to approximately0.5 inches long, etc.). It should be apparent, however, that theinvention can be fabricated in any size and shape depending oncircumstances.

One advantage of this embodiment is that the sensing membranes 14′ and14″ can be manufactured in a separate piece that is placed over, e.g.,slipped onto, the sensor capsule 3″ following the above-describedassembly process. In this manner, the membrane manufacturing steps canbe advantageously separated from the electronics and encapsulationmanufacturing steps.

In one preferred embodiment, the sleeve S is made with a plasticmaterial (e.g., preferably, made with polyethylene and most preferablyof a medical grade polyethylene (e.g., UHMWPE (ultra high molecularweight polyethylene)). The sleeve can be manufactured from anyappropriate material depending on the circumstances and the particularuse of the sensor. For example, when the sensor is used in-vivo, thesleeve can be constructed from biocompatible materials—some additionalpreferred, non-limiting, examples of biocompatible materials includepolypropylene, PMMA, polyolefins, polysulfones, ceramics, hydrogels,silicone rubber and glass. The sleeve S is preferably an injectionmolded plastic sleeve sized such that the internal diameter of thesleeve can be precisely fit over the capsule. When assembled onto thecapsule, the sleeve S preferably has sufficient elasticity to allow atight mechanical fit that will not easily come off of the capsule 3″.The sleeve S is preferably formed with holes, pockets, or cavities H toaccommodate the indicator membranes 14′ and 14″ (e.g., to mechanicallyentrap the membranes). For example, fluorochrome pockets H can bereadily insert molded in the sleeve. FIGS. 19(A)-19(I) demonstrate avariety of arrangements of the holes, etc., H on various sleeves S thatcan be utilized in various embodiments. Notably, the sleeve S should beconfigured such that when mounted on the capsule 3″, the holes, etc.,can be aligned sufficiently with the respective photosensitive elements20-1 and 20-2. The device shown in FIGS. 17(A)-17(B) preferably has asleeve constructed like that shown in FIG. 19(E)—e.g., with the holes Hhaving an oval shape disposed substantial over the surface of thephotosensitive elements. Alternatively, although less preferred asdiscussed above, the indicator membranes could be formed on theperimeter surface of the sleeve (e.g., so as to bulge outward therefrom)without such pockets therefor.

Another advantage of using an outer sleeve S is that the materials(e.g., discussed above) that can be used therefor can have good medicalgrade surfaces for subcutaneous tissue to bind to, which canadvantageously help prevent the device from movement and migrationwithin a patent, in-vivo, when the sensor is of the type implantedwithin a person (or within another animal). In addition, natural partinglines and roughness of the edges of such a molded sleeve can also helpprevent such movement and migration. Prevention of movement or migrationafter implantation can be very important in some embodiments—forexample, so that inductive power and telemetry coils can be maintainedin optimal alignment between the implanted device and an externalreader.

In other alternative constructions, the sleeve S could also be extrudedin the shape of a tube (e.g,. into a cylinder like that shown in FIG.19(I), discussed below) and applied on the capsule with a compressionfit. In addition, the sleeve S could also be formed into a tube that isheat shrunk onto the capsule 3″. The membrane pockets H could also beformed therein by molding, cutting, laser machining, or laser drilling.In addition, in some designs, thousands of small laser machine holes Hcan be fabricated in the side wall of the sleeve S.

Another advantage of using a membrane sleeve S is the ability to protectthe indicator and reference membranes during manufacture, handling,storage, and, most importantly, during injection through a trocar intothe subcutaneous tissue as is to be performed in some preferredembodiments. The mechanical forces and movement while implanting thesensor through a metal trocar may damage the exterior of the device ifthe surface is not adequately protected.

While a variety of exemplary membrane sleeves S have been described,various other membrane materials, sizes, locations, geometrical designs,methods of manufacture, etc., could be employed by those in the art inview of the above.

Once again, the arrangement of the parts within the sensor can also bevaried by those in the art. For example, FIGS. 17(C)-17(D) show a secondembodiment similar to the embodiment shown in FIGS. 17(A)-17(B) with theindicator membrane 14′ and the reference membrane 14″ on the same sideof the circuit board 70 and with a single radiation source, e.g., LED,18—similar to the embodiments shown in FIGS. 14(A)-14(C). All of theapplicable variations described above with respect to FIGS. 14(A)-14(C)and to FIGS. 17(A)-17(B) could be applied to the embodiment shown inFIGS. 17(C)-17(D).

As another example, FIGS. 17(E)-17(F) show another embodiment similar tothe embodiment shown in FIGS. 17(A)-17(C) with the indicator membrane14′ and the reference membrane 14″ on the same side of the circuit board70 but with two radiation sources, e.g., LEDs, 18-1 and 18-2 similar tothe embodiments shown in FIGS. 15(A)-15(C) but with the LEDs spacedfurther apart in the illustrated example. All of the applicablevariations described above with respect to FIGS. 15(A)-15(C) and toFIGS. 17(A)-17(C) could be applied to the embodiment shown in FIGS.17(C)-17(D).

While the embodiments described herein-above included one indicatorchannel and one reference channel, as noted above the variousembodiments described herein-above can be modified so as to include aplurality of indicator membranes (e.g., measuring the same or differentanalytes) and/or a plurality of reference membranes (e.g., measuring thesame or different optical properties). In addition, it is noted that theprinciples related to the provision of a sensor 10 having a two partconstruction like that shown in FIGS. 17(A)-17(F) could also be employedwithin a basic sensor as described herein-above that does not utilizesuch a reference channel—for example, FIGS. 18(A)-18(B) illustrate anembodiment with a single photosensitive element 20 and a single source18 that can be used to obtain a sensory reading as described above withreference to FIGS. 1-13 without a reference channel reading.

While FIGS. 18(A)-18(B) were described as being without referenceindication, it is noted that a device having a single source and/or asingle photosensitive element could still be used to provide separateindicator and reference readings in some embodiments, such as forexample: a) a single LED may alternate emissions in differentfrequencies for alternating indicator and reference channel readings; b)in cases where the indicator membrane and the reference membrane havedifferent frequency characteristics of radiation emission, a filter overthe photosensitive element could be adapted to alternate passage of suchdifferent frequencies to the photosensitive elements; c) in cases wherethe indicator membrane and the reference membrane have different timecharacteristics of radiation emission, the device could be adapted toprovide a time delay reading for the indicator channel and the referencechannel (e.g., the indicator channel could have picosecond decay whilethe reference channel has nanosecond decay or vise-verse); d) etc.

As described above, FIGS. 19(A)-19(I) show some examples of alternativesleeve S and pocket H designs. It is noted that the devices shown inFIGS. 17(C)-17(F) preferably include a sleeve S like that shown in FIG.19(E), configured such that the pockets H can be readily aligned overthe respective photosensitive elements. In addition, the sleeve designcould be like that shown in FIG. 19(I) wherein the sleeve S is formedinto a tube that is open at both ends and that can be slid over thecapsule. In addition, a plurality of sleeves S could also be employed(e.g., each to contain a respective membrane), such as shown in FIG.19(A) wherein two sleeves S can fit over opposite ends of the capsule.In embodiments like that shown in FIGS. 19(D), 19(G) and 19(H), whereinpockets are provided around the perimeter of the sleeve S, the sleevecan be applied over the capsule without having to orient the sleeve andthe capsule exactly in certain embodiments when the photosensitiveelements are on one side of the circuit board 70 (e.g., when twochannels are used, the pockets towards the left side of sleeve cancontain reference membranes while the pockets at the right side cancontain indicator membranes). Once again, these are merely exemplarydesigns and a variety of other sleeve and/or pocket designs could bemade by those in the art.

FIG. 19(J) shows yet another embodiment of the invention wherein thesleeve S is made with an outer annular flange F. The annular flange F ispreferably formed so as to naturally (e.g., in an unbiased state) extendlaterally outward from the side of the sensor as shown. Preferably, theflange F is made of absorbable or biodegradable material. The embodimentshown in FIG. 19(J) can be used, for example, in applications wheremigration prevention is desired. For instance, even when connectivetissue is expected to hold the sensor in place over time, thisembodiment can facilitate maintenance of proper positioning even priorto ingrowth of connective tissue. That is, the annular flange can helpprevent movement of the sensor within a medium in which it is applied orinserted (e.g., such as within a patient). In a most preferredembodiment, the flange is flexible and is capable of bending over (e.g.,to a position shown in dashed lines in FIG. 19(J) upon insertion in thedirection of the arrow A into a trocar tube TT) such that the sensor canbe inserted into a patient. Then, after inserting the sensor 10 into apatient through the trocar tube and then withdrawing the trocar tube TT,the flange F will resume its original shape (or substantial resume thatshape) and facilitate maintenance of the sensor in its proper insertedposition. As noted, the flange F is preferably made of an absorbable orbiodegradable material such that after a certain period of time theflange F will degrade—e.g., so that the sensor can be: a) easilyremoved; b) maintained in place via other means (e.g., such as viacapillary ingrowth as described herein-above); and/or c) for otherreasons. In alternative embodiments, a plurality of flanges F can beprovided. In other alternative embodiments, the flange F can extend onlypartly around the circumference of the sensor (as opposed to completelyannularly therearound). The sleeve S shown in FIG. 19(J) preferablyincludes respective indicator and control indicator molecules (e.g.,within membranes in the pockets H) as described herein-above. However,it is contemplated that an annular flange F could be provided around asensor of any of the embodiments disclosed herein, even where such asleeve S is not included. In that regard, one or more flange F (e.g.,preferably biodegradable) could be affixed to the exterior of any of thesensors described herein for similar functions and purposes. While theannular flange F is shown as being generally flat (e.g., with agenerally rectangular cross-section), the flange F could also have othercross-sectional shapes—for instance, a band of suture material(preferably biodegradable) could be wrapped around the sensor. While theflange F preferably is capable of flexing inward and outward as shown,in certain embodiments the flange or band could also be made withoutsuch capabilities.

It is contemplated that the particular sensor construction (andespecially the particular locations of the indicator membrane 14′ andthe reference membrane 14″ in the sensor) can be selected based in partupon the particular environment within which the sensor is to be used.Notably, the indicator molecules (i.e., in the indicator membrane) andthe control indicator molecules (i.e., in the reference membrane) shouldbe exposed to substantially the same environment (i.e., to theenvironment containing the analyte being sensed). Accordingly, themembrane locations on the sensor will depend in part on the methods ofuse. As some examples: a) if a sensor is placed with its longitudinalaxis vertical in a solution in which an attribute being tested may varybased on depth within the solution (e.g., within a wine bottle, etc.),it may be desirable to use, for example, one of the sensor constructionsshown in FIGS. 16-17 wherein photosensitive elements are at like axialpositions but on opposite sides of the sensor so that the membranes 14′and 14″ can be disposed at like vertical elevations; while b) if asensor is to be used, for example, sub-cutaneously with its axisgenerally parallel to the skin of the patient, it may be desirable touse, for example, one of the sensors shown in FIGS. 14(A) or 15(A).Among other factors, it should be understood that the sizes andlocations of the membranes 14′ and 14″ (and the pockets H containingsuch membranes) will also depend in part on the field of view of theradiation source(s), e.g., LED(s), selected.

FIGS. 20(A)-20(B) show another embodiment that is similar to theembodiment shown in FIGS. 17(C)-17(D) except that the sleeve S isreplaced by a removable film F. As shown, the film F includes theindicator membrane 14′ and the reference membrane 14″ thereon. As withthe sleeve S, the membranes 14′ and 14″ are preferably formed withinpockets, but, although less preferred, the membranes could also beformed on the film surface. The film F can be made of the same types ofmaterials as the sleeve S as described above. The film F is preferablyremovably attachable on the capsule via the tackiness or adhesiveness ofthe material of the film itself or via an adhesive that will notappreciably affect the transmission of the radiation (e.g., light) toand from the indicator membranes (as one example, an adhesive like thatused for POST-IT™ notes manufactured by 3M Corporation could be appliedbetween the film F and the capsule 3″). The film F is preferably sized,as shown, so as to be large enough to support the indicator membrane 14′and the reference membrane 14″ at their appropriate locations on thecapsule 3″. As shown, to remove the film F, for example, the corner Ccould be pulled and the film F can be removed in a similar manner to theremoval of a BAND-AID™ adhesive bandage from a person's skin.

The various other embodiments shown herein-above could also be modifiedso as to include a film F rather than a sleeve S. In addition, while arectangular film member F is shown, the film can be constructed in othershapes and forms depending on circumstances at hand. In addition, pluralfilms F could also be used, such as for example including separate filmsfor the reference and indicator membranes.

Thus, the embodiment shown in FIGS. 20(A)-20(B) and the variousalternatives thereof can have a variety of benefits similar to thatavailable with embodiments utilizing a removable sleeve S as describedherein-above.

FIGS. 22(A)-22(C) show another embodiment of the invention wherein ashielding sleeve S′ is formed around the body 12. In this embodiment,the sleeve S′ is constructed to provide shielding from outside light.Two problems associated with sensors, such as with fluorescent glucosesensors, involve light other than that emitted by the radiation source18. One source of light is from ambient sources such as sunlight andartificial lighting. Light of sufficient intensity can potentiallysaturate the sensor, rendering it useless for sensing fluorescent light.In addition, most artificial light sources have a significant AC (timevarying) component; although filtering techniques can be employed toattenuate this source of noise, it can still significantly degrade thesignal obtained. Another source of stray light is fluorescent emissionof materials outside the sensor. This latter problem is particularlydifficult in that the resulting signal generally cannot beelectronically filtered from the indicator fluorescence. The embodimentshown in FIGS. 22(A)-22(C) can be used to substantially eliminate theseeffects from outside light interference.

In one preferred construction, the sleeve S′ is formed from asubstantially optically opaque, substantially non-reflective, layer ofmaterial containing a plurality of small holes H extending therethroughfrom its outer surface to the membranes 14′ and 14″. In one exemplaryembodiment, the sleeve S′ can be made with a black teflon tubing thatis, for example, heat shrunk onto the body 12. Nevertheless, the sleeveS′ can be formed with any suitable material. The holes H are preferablyformed at an angle that is transverse to, and preferably substantiallyorthogonal to, the respective directions of propagation RL of light fromthe radiation source to the membranes 14′ and 14″ (e.g., see anglesθ_(1 and) θ₂). The diameter of each hole H is preferably sufficientlysmall to substantially prevent light from passing directly from theradiation source 18 out of the sensor, and yet is preferablysufficiently large to allow analyte diffusion, or penetration, to themembranes 14′ and 14″. The number of holes H is preferably selected toallow relatively unrestricted diffusion of the analyte into themembranes. Thus, while some ambient light AL, see FIG. 22(C), may enterthe sensor through the holes H, the penetration of ambient lighttherethrough should be largely attenuated.

FIG. 22(D) shows another alternative embodiment, wherein an inner glasscapsule 3″ is employed within an outer glass capsule 3′″ (otherembodiments could use an outer glass sleeve) with an indicator membrane14′ and a reference membrane 14″ between the two capsules and with lasermachine holes h through the outer capsule to allow analyte (e.g.,glucose) migration into the indicator membrane 14′. It should beapparent based on this disclosure that other internal components (e.g.,similar to that shown in FIGS. 16(A)-16(B)) would be included and, thus,such components are not be further described or shown with reference toFIG. 22(D).

FIGS. 23(A)-23(C) show yet another embodiment of the invention wherein asingle LED 18 is used to excite both indicator molecules in theindicator membrane 14′ and control indicator molecules in the referencemembrane 14″.

Typically, LEDs (e.g., LED chips) are manufactured by growingcrystalline layers of semiconductor material 18-C (e.g., epitaxy) upon asubstrate material 18-S. LED chips can be made very small—for example,the entire thickness of the semiconductor layers can be less than about10 μm, or even less than about 5 μm, or even thinner. Typically, thesubstrate upon which the semiconductor layers are formed issubstantially thicker—for example, greater than about 50 μm, or evengreater than about 100 μm, or even thicker.

LEDs are traditionally used to emit light from a top side 18-A of theLED opposite the surface on which the LED chip is mounted (e.g., areflector cup surface). As schematically shown in FIG. 23(D), an LEDchip 18 is typically placed within a reflector cup 18-RC which ensureslight transmission in an upward direction UD. As shown in FIG. 23(D),one or two small wires 18-W are typically connected to the top surface18-A of the chip 18 (e.g., via gold contacts). In addition, thesubstrate 18-S is typically substantially transparent such that lighttransmitted by the semiconductor material is internally reflected withinthe substrate and reflects off the reflector 18-RC, preventingtransmission through the bottom of the LED 18-B. In fact, it has beengenerally considered in the art that LED chips are only for emission oflight in a direction outward from the top surface 18-A of the LED chip.

The present inventors have found, however, that an LED chip 18 can bemade to effectively emit light from both the top side 18-A and thebottom side 18-B of the LED chip. In one preferred embodiment, as shownin FIGS. 23(A)-23(C), the LED chip 18 is formed on a substantiallytransparent substrate (appropriate transparent substrate materials caninclude, for example, sapphire, silicon carbide and other suitablematerials) that is mounted transverse to the top surface of the circuitboard 70 (e.g., on a mount 18-m as shown) (preferably, the top andbottom surfaces 18-A and 18-B of the LED are arranged generally tomaximize illumination of the indicator and reference channel and/or tomaximize internal illumination of the sensor body). Preferably, a mask34 is also included to inhibit cross-talk between the indicator channeland the reference channel.

In this manner, a single LED can be effectively used to illuminate bothan indicator membrane 14′ and a reference membrane 14″. FIG. 24(B) is anillustrative example of a field of illumination from a known LED whenconventionally mounted upon a non-transparent flat surface. The anglesof 0 degrees and 180 degrees are parallel to the flat LED chip topsurface, while 90 degrees is perpendicular thereto. As shown,illumination is substantially only from one side of the LED chip—i.e.,from the top side 18-A. In contrast, FIG. 24(A) illustrates one exampleof illumination that can be achieved through both upper and lower sides,18-A and 18-B, of an LED chip 18. In FIG. 24(A), the right side of thefigure from 0 degrees to 90 degrees represents the light transmittedthrough the bottom 18-B of the LED, while the left side of the figurefrom 0 degrees to −90 degrees represents the light transmitted throughthe top side 18-A of the LED. Thus, as shown in this example, a largeamount of light can actually be emitted from the bottom side 18-B of theLED. In this illustrative case, a greater amount of light is actuallyemitted from the bottom side 18-B of the LED, which may be due, forexample, to the presence of wires, electrical contacts (e.g., typically,one or more gold contacts are applied on top of an LED chip 18), orother materials on top of the top side of the LED chip. The measurementsshown in FIG. 24(A) were obtained utilizing a MODEL LED-1100™ Gonometricanalyzer made by Labsphere, of North Sutton, N.H. The LED used in FIG.24(A) was a #NSHU550E™ LED by Nichia Chemical Industries, LTD, Tokyo,Japan. The LED used in FIG. 24(B) was a C470-9™ LED from Cree Research,Inc., of Durham, N.C.

In these embodiments wherein light is radiated both what is typicallyconsidered to be the top side 18-A and the bottom side 18-B of the LEDchip to excite both indicator and control indicator molecules with asingle LED, preferably a sufficient amount of light is transmitted bothabove and below the LED to sufficiently illuminate both channels.Preferably, the amount of light transmitted from one side is about 6times or less, the amount of light transmitted from the other side, ormore preferably about 4 times of less, or more preferably about 2 timesor less, and in more preferred embodiments about equal. However, theamount of light radiated above and below the LED can vary significantlydepending on circumstances.

FIG. 25(A)-25(B) show a sensor 10 according to another embodimenthaving: a) a sensor body with a machined peripheral recess 12C around acircumference of the sensor body that contains an indicator membrane 14;b) a substrate 70 with a hole or window 70H beneath a radiation source(e.g., an LED) 18; and c) an optical deflector D with a generallytriangular cross-section extending around the circumference of thesensor body. This embodiment is otherwise like that shown in FIGS.14(A)-14(B). Electrical and other components (not shown) are like thatdescribed herein-above, and, thus, need not be further described withrespect to FIGS. 25(A)-25(B).

In the embodiment shown in FIGS. 25(A)-25(B), the radiation source 18emits radiation through its top and bottom sides 18-A and 18-B, as inembodiments described above. Radiation L, shown by arrows, is reflectedwithin the sensor body, as in embodiments described above. As shown,radiation emitted through the window or hole 70H is reflected within thesensor body in such a manner that radiation from the top and bottomsides of the radiation source is used for detection. As shown, thesensor body 12 preferably includes a radiation deflector D situated suchthat radiation emitted generally vertically (i.e., above the top side orbelow the bottom side) from the radiation source is reflected laterallyfor better distribution and internal reflection and/or for ensuring thatradiation is directed to outer regions of the indicator membrane. Whilethe embodiment shown in FIGS. 25(A)-25(B) includes both indicator andcontrol channels, it should be understood by those in the art based onthis disclosure that the control channel can be eliminated in otherembodiments and/or that any other modifications described herein withrespect to other embodiments can also apply to the embodiment shown inFIGS. 25(A)-25(C) where appropriate.

FIG. 26 shows another embodiment of a sensor 10 having a substantiallyoptically transparent circuit substrate 70. The substantially opticallytransparent circuit substrate 70 allows radiation to pass through thesubstrate 70. This facilitates the permeation of both excitationradiation and, in the non-limiting example of a fluorescent indicator,emission radiation throughout the sensor body 12, enabling moreradiation to be received by the photosensitive members. As a result, thesignal detection area can be increased (e.g., by signal capture at thetop and bottom sides of the photosensitive elements) to substantiallyenhance signal detection.

Preferably, the radiation source 18 is mounted on the substrate 70 insuch a manner that radiation is also emitted from the bottom side of theradiation source. The embodiment shown in FIG. 26 can, thus, begenerally similar to that shown in FIGS. 23(A)-23(C) with respect toradiation being emitted from the top and bottom sides of the radiationsource 18. Alternatively, radiation could be transmitted from only oneof the top or bottom sides. The radiation source preferably includes anLED that is optically coupled to the optical substrate 70 (such as, forexample, with an optical epoxy) to guide excitation light into thesubstrate.

The optically transparent substrate 70 can be made with, for example,sapphire, quartz, silicon carbide, GaN or other inorganic substratematerials that can be patterned with metallization. Other organicpolymeric materials may also be used to fabricate the substrate. Anysubstantially clear material which can support the manufacturing ofprinted or etched electronic circuits can be used for this application.Other appropriate materials apparent to those in the art based on thisdisclosure can also be used. In one exemplary, but non-limiting,construction, the substrate 70 is made with quartz. Various vendorsoffer quartz substrates because such substrates are advantageous inother unrelated applications in the telecommunications industry, such asin high frequency applications. For example, MIC Technologies™ (anAeroflex Company, 797 Turnpike St. North Andover, Mass. 01845) offersquartz substrate fabrication as a circuit substrate option. Thesubstantially optically transparent substrate can then be used, withmethods well known in the art, to attach parts using a standard hybridcircuit attachment method (e.g., conductive epoxy, solder, wire bonding,non conductive epoxy, etc.). Once all of the parts have been attached,the entire circuit can be, for example, immersed in a monomer solutionand then a polymer reaction can be, for example, initiated using heat orradiation, such that a circuit can be formed that is potted, enclosed,and sealed within a waveguide polymer (e.g., PMMA)(i.e., as describedherein-above).

As indicated above, the embodiment shown in FIG. 26 preferably includesphotosensitive elements that can detect radiation directed at their topand bottom sides. Typically, photosensitive elements can only detectradiation directed at their top sides. In one preferred construction,the photosensitive elements include photoresistors.

A photoresistor is routinely fabricated by a simple chemical depositionprocess which places a photosensitive chemical substance within acircuit. When photons contact the surface of the deposited material, achange in resistance occurs and the circuit thus varies its resistanceas a function of incident light intensity. Typically, the photoresistivematerial is deposited on opaque substrates such as ceramics. This causesthe resultant photoresistor device to be sensitive in only one directionbecause light cannot penetrate the opaque substrate from the bottom side(i.e., the side adjacent the substrate).

In common applications of photoresistive detectors, this“unidirectional” construction is adequate. In preferred embodiments ofthe present invention, however, both excitation and emission light isdispersed throughout the device.

Two notable objectives in preferred embodiments of the invention are tomaximize the amount of light from the excitation source which isincident on the indicator membranes and to maximize the amount offluorescent signal light which is captured by the photosensitiveelements. Contrary to these objectives, opaque circuit substrates (suchas those made of ceramic, polyimides, fiberglass, etc.) can block asubstantial amount of light from propogating throughout the device and,thus, can reduce the overall sensitivity of the sensor. On the otherhand, the embodiment illustrated in FIG. 26 can greatly promote both ofthese objectives. By depositing the detector material on a substantiallyclear substrate, the substrate can function as a larger area capturewaveguide and can thereby convey, for example, additional fluorescentsignal light to the photosensitive element. Furthermore, by mounting theradiation source, e.g., LED, onto a substantially clear substrate,substantially all of the radiation, e.g., light, radiated from theexcitation source, can be more uniformly propagated throughout thedevice and, thus, more uniformly, and with greater power efficiency,directed to the indicator membrane.

The embodiment shown in FIG. 26 is not, of course, limited tophotoresistive detectors, but other photosensitive elements can be used,such as, for example, photodiodes, transistors, darlingtons, etc., whereappropriate.

When radiation is received at both sides of the photosensitive elements,high pass filters 34A and 34B are preferably provided above and belowthe photosensitive elements 20-1 and 20-2 in order to, for example,separate excitation radiation from fluorescent emission radiation. Thehigh pass filters can be used, if desired, to adjust the spectralselectivity for the photosensitive elements. A high pass filter can beinstalled on both sides of the photosensitive elements by applying, forexample, a filter epoxy, such as that available from CVI Laser, andothers as described above with respect to the embodiment shown in FIG.1.

Rather than, or in addition to, using filters 34A and 34B, thephotosensitive elements can be made with materials that can be adapted,e.g., tuned, to be sensitive to particular wavelengths. Thephotosensitive elements could, thus, be able to be tuned tosubstantially sense, for example, fluorescent emission radiation ratherthan excitation radiation from the radiation source. In this regard,photoresistive detectors can be chemically tuned to be sensitivesubstantially at a specific wavelength, thereby reducing or eliminatingthe need for a separate filter element. Appropriate materials arereadily commercially available. Known devices are produced and sold by,for example, Silonex Inc.™, (2150 Ward Ave, Montreal, Quebec, Canada,H4M 1T7) where peak wavelength sensitivity is adjusted and optimizedbased on varying ratios of dopants and mix ratios within a cadmiumsulfide base (and others).

Although discussed in reference to the embodiment of FIG. 26, the“tunable” photosensitive elements described herein can also beadvantageously incorporated into any of the embodiments described hereinin other embodiments of the invention.

The embodiment shown in FIG. 26 preferably operates like embodimentsdescribed herein-above. To avoid unnecessary repetition, elements of thesensor shown in FIG. 26, e.g., electronic components, etc., are notshown and/or not described in relation to this embodiment. It iscontemplated that the embodiment shown in FIG. 26 can be modified bythose in the art in the same manner as any of the other embodimentsdescribed herein where appropriate.

FIGS. 27(A)-27(C) show another embodiment of a sensor 1000 with aninternal heater. In the illustrated example, the sensor 1000 is notnecessarily required to include a circuit substrate embedded entirelyinside a waveguide, capsule or the like. It is contemplated, however,that a heater of this embodiment can be employed in any of theembodiments described herein, or in any other appropriate sensorhousing. In the illustrated example, the sensor 1000 has a chip-likeconstruction with a generally rectangular configuration with leads 1110extending therefrom. The leads can be used to provide power, signals,etc., to and/or from the sensor.

The embodiment shown in FIGS. 27(A)-27(C) incorporates several uniquedesign features having particular advantages in, for example, thedetection and measurement of analytes in humidified gases. In apreferred, but non-limiting, example, the illustrated device is used asan oxygen sensor. Exemplary applications include, but are not limitedto, the breath-by-breath measurement of oxygen during the respiration ofhumans or animals—e.g., where the sensor is exposed to cool/dry airduring inhalation and to warm/humid breath during exhalation. Theillustrated design can accurately measure, for example, the oxygencontent during all phases of temperature and water vapor (humidity)variation. While the illustrated example is preferably used for themeasurement of oxygen, other examples can be used to measure otheranalytes—for example, sensitive membranes for the measurement of carbondioxide, another gas, or several gases could be employed.

In summary, in the illustrated example, the sensor 1000 includes a cover1200 having a top wall 1210 with an opening 1220 and four depending sidewalls 1230. The bottom of the cover is configured to fit on top of asubstrate 700 to form a box-like enclosure. As shown, the substrate 700has photosensitive elements 20-1 and 20-2, a radiation source 18 andother electronic components (not shown), and a heating element 1400mounted thereon. In the illustrated embodiment, the heating element 1400extends over the photosensitive elements 20-1 and 20-2. The heatingelement has cut-out openings 1410 to allow radiation from the source 18to pass to membranes 14-1 and 14-2 which are preferably located abovethe heating element. As shown, the membranes are preferably exposed viathe hole 1220 in the cover 1200. The entire region R between the heatingelement, the sensor membranes and the substrate preferably contains awaveguide material as in embodiments described herein-above.

The heating element 1400 can be made with any appropriate material(e.g., heat conductive material(s)), such as for example copper alloys,other heat conductive metals, or the like. The heating element 1400 canbe made from any material having appropriate thermal properties. Inorder to heat the heating element 1400, the substrate 700 preferablyincludes a plurality of heat generators 710 (e.g., heater resistors orsemi-conductor resistors) thereon that transfer heat to the heatingelement. In the illustrated, but non-limiting, embodiment, four heaterresistors 710 are utilized. The heat generators 710 are preferablylocated adjacent (e.g., contacting or sufficiently close to) the sidesof the heating element 1400 to transfer heat thereto.

The heating element 1400 serves, for example, the following twopurposes: 1) keeping the signal and reference membranes 14-1 and 14-2 atsubstantially the same thermal equilibrium; and/or 2) heating themembranes 14-1 and 14-2 to a temperature that is above the dew point ofhumidified gases to be measured. In the example of human respiratorymonitoring, this temperature value can be, for example, slightly aboveabout 37° C. In one exemplary construction, the invention employs athermal set point of about 40° C. by the use of heat resistors 710 and afeedback thermistor 711. In an exemplary construction, the heatresistors 710 include four 390 ohm ½ W surface mount resistors that arein parallel. In alternative embodiments, other numbers of heatgenerators 710 and/or other types of heat generators 710 (such asscreened resistors, thick film resistors, heater tape, etc.) can beemployed. In addition, alternative embodiments can utilize other formsof temperature control. Notable methods of temperature control use oneor more thermistor, thermocouple, RTD, and/or other solid-statetemperature measurement device for temperature control. Preferredembodiments, however, utilize a thermistor 711 in view of the lowercosts.

A notable advantage of heating the membrane surfaces is the preventionof moisture condensation at the sensor surface. When a condensationlayer is formed, the condensation layer can cause optical scattering andaberrations at the sensor surface, which substantially reducemeasurement accuracy when utilizing, for example, an fluorescenceamplitude mode based measurement. The condensation layer can also reducethe gaseous response time of the sensor because the mass diffusionproperties at the sensor surface can be altered. It should be noted thatby measuring the time-decay or phase properties of the fluorochrome, theaccuracy of the sensor can be improved because the measurement issubstantially not affected by amplitude variation. The time-decay orphase mode of measurement does not, however, mitigate any response timedegradation because this is diffusion based at the sensor surface.

This embodiment can also provide other notable advantages that areparticularly beneficial for use in, for example, the preferred, butnon-limiting, embodiments as an oxygen sensor, as well as in otherapplications. In particular, a significant advantage of this embodiment(and in other embodiments described herein as well) is the ability ofthe sensor to respond extremely quickly to a step change in criticalrespiratory gasses such as oxygen and CO₂. With this embodiment,response rates of 100 milliseconds or faster (some as fast as 30-40milliseconds) can be achieved, enabling an almost real-timedetermination of respiratory gas content (here: response time is definedas the time required for the output of the sensor to change from 10% to90% of steady-state level upon application of a step change in thepartial pressure of the gas in question).

The ability of this embodiment to, for example, observe and measuresubstantially real-time waveforms and oxygen levels from inhaled andexhaled respiratory gasses has significant medical utility. Arespiratory gas sensor with this fast response characteristic can beutilized, for example, in conjunction with flow or volume measuringdevices to determine the uptake and release of respiratory gasses,enabling the measurement of critical medical parameters such asmetabolic rate (calorie expenditure), indirect cardiac output based onthe Fick principle (first described in theory by Adolph Fick in 1870),pulmonary function, and onset of shock. Many of these medical diagnosticdeterminations require the measurement of the partial pressurerespiratory gasses at the very end of an exhalation (known as end-tidalp02 or end-tidal pCO2 levels). Because the amount of time between theend of a normal exhalation and the inhalation of the next breath isextremely short, a very fast response sensor can be important todetermine end-tidal levels which have not been already affected by theinhalation of fresh air from the subsequent next breath. In addition tohaving a sensor with a sufficiently fast response time to a change ingas concentration, the sensor should also have the ability to compensateequally quickly to the changes in the temperature and humidity levels inthe inspired and expired gasses. In the preferred embodiments, this hasbeen achieved through the employment of a reference channel, asillustrated. The present invention is also advantageous in that itenables medical diagnostic procedures to be performed non-invasively andwithout the need for expensive analytical instruments that are otherwisecurrently used to make similar determinations with the current art.

FIGS. 28(A) and 28(B) illustrate actual test data of a step change inthe partial pressure of a gas in one exemplary construction of theembodiment of FIGS. 27(A)-27(C). In particular, FIGS. 28(A) and 28(B)depict actual response time determinations employing a construction ofthis embodiment for use in the, non-limiting, example as an oxygensensor. FIG. 28(A) is a measurement of the response time of the sensorto a step change from ambient air (approximately 21% oxygen) to 100%oxygen which was supplied from a certified compressed gas cylinder (theresponse time of a sensor from a lower to a higher analyte concentrationis typically referred to as “recovery time”). FIG. 28(B) is ameasurement of the response time of the same sensor to a step changefrom 100% nitrogen supplied from a certified compressed gas cylinder toambient air. The recovery and response times were, in these illustrativebut non-limiting examples, about 41.2 and 32.1 milliseconds (as shown),respectively, as determined with a Tektronix Model TDS™ two channeloscilloscope. Preferably, recovery and response times are under about100 milliseconds, and more preferably under about 80 milliseconds, andeven more preferably under about 60 milliseconds. Preferred embodimentshave a range of about 40 to 80 milliseconds.

In operation, the sensor 1000 operates like the two channel embodimentsdescribed herein-above. In this embodiment, however, the heat generators710 impart heat to the heating element 1400 which in turn acts as aspreader to distribute heat within the sensor and within the membranes14-1 and 14-2.

The cover 1200 is preferably formed from an insulating material, e.g.,from an elastomer such as plastic or the like. In this manner, the cover1200 can help conserve heat and maintain a temperature of the membranes.As a result, the heater does not need to work as hard or to consume asmuch power to operate. In the illustrated embodiment, the membranes 14-1and 14-2 are also preferably recessed below a top surface of the hole1220 when assembled as shown in FIG. 27(A) so that the membranes areless likely to be subject to external factors or to become damaged. Thecover 1200 can be made, for example, by injection molding or by anotherappropriate means.

The cover 1200 is optional and can be eliminated in some cases. However,the cover 1200 is preferred because it can advantageously provideinsulating properties for the heating element 1400, enabling the use ofa smaller heating element and improved uniformity of heat distributionto the sensing and reference membranes, especially under conditions ofrapid thermal changes and/or high flow velocities in the medium in whichthe analyte is contained. The cover is, thus, preferably installed overthe sensor to assist in the performance of the heating element 1400and/or to direct gases at the membrane surfaces.

As indicated, the sensor 1000 preferably utilizes two photosensitiveelements 20-1 and 20-2. Preferably, the photosensitive element 20-1detects oxygen signal fluorescence from a indicator channel membrane14-1 and the photosensitive element 20-2 detects a signal from thereference channel membrane 14-2. Preferably, the reference channelmembrane 14-2 is substantially not sensitive to oxygen, but is sensitiveto temperature to substantially the same extent as the signal channelmembrane 14-1. This is a notable feature in cases where the device isused for detecting oscillatory breathing (i.e., inhale/exhale) of ahuman or another animal because of the temperature and water vaporchanges. With this embodiment, the temperature equilibrium of theindicator and reference channels can be maintained via the heatingelement 1400.

In the illustrated example, the membranes 14-1 and 14-2 are eachpreferably made with a borosilicate glass substrate of substantiallyequal thickness. Preferably, the membranes 14-1 and 14-2, thus, havesimilar thermal properties. A preferred matrix for the sensing ofgaseous or dissolved oxygen or other gasses is an inorganic polymersupport matrix termed sol-gels or ormosils, into which the indicatormolecule is immobilized or entrapped. These materials and techniques arewell known (See, e.g.: McDonagh et al., “Tailoring of Sol-Gel Films forOptical Sensing of Oxygen in Gas and Aqueous Phase”, AnalyticalChemistry, Vol. 70, No. 1, Jan. 1, 1998, pp. 45-50; Lev. O. “OrganicallyModified Sol-Gel Sensors”, Analytical Chemistry, Vol. 67, No. 1, Jan. 1,1995; MacCraith et al., “Development of a LED-based Fibre Optic OxygenSensor Using a Sol-Gel-Derived Coating”, SPIE, Vol. 2293, pp. 110-120('94); Shahriari et al., “Ormosil Thin Films for Chemical SensingPlatforms”, SPIE, Vol.3105, pp. 50-51 ('97); Krihak et al., “Fiber OpticOxygen Sensors Based on the Sol-Gel Coating Technique”, SPIE, Vol. 2836,pp. 105-115 ('96), the entire disclosures of which are each incorporatedherein by reference). These types of membranes can be applied to theappropriate substrate by a number of techniques that are well known inthe art, such as dipping, swabbing, squeegeeing, silk screening, padprinting, vapor deposition, ink-jet printing, etc. These types ofmembranes can also be advantageously incorporated into any otherembodiment of the invention described herein where appropriate.

Preferably, each membrane is, thus, formed with a glass (e.g.,borosilicate glass) substrate that is coated with a thin-film sol-gelmatrix coating that utilizes the same base chemistry in each membrane.Preferably, the reference membrane 14-2 is further processed to blockoxygen diffusion. In examples of this embodiment for sensing 02, apreferred indicator molecule includes, as one example,tris(4,7-diphenyl-1,10-phenanthroline)ruthenium (II) perchloratemolecule, discussed on column 1, line 17, of U.S. Pat. No. 5,517,313,the disclosure of which is incorporated herein by reference in itsentirety. It is contemplated that the membranes can include a variety ofother materials as set forth herein-above in other embodiments of theinvention.

The radiation source preferably includes an LED (e.g., blue) that ismounted such that its light output is waveguided to the indicator andreference channel membranes 14-1 and 14-2 through the waveguide materialwithin the region R. In an exemplary embodiment, the waveguide materialis Epoxy Technologies 301™ which has good optical characteristics,although other appropriate materials could also be used. Preferably,fluorescent emissions from the membranes are similarly waveguided to thephotosensitive elements 20-1 and 20-2 which are mounted on the substrate700. Preferably, an optical filter 34 is provided for each of thephotosensitive elements. In exemplary embodiments, as described above,each optical filter 34 can include a filter epoxy, such as filter resinavailable from CVI Laser, with, for example, a 600 nm cutoff surroundingthe photosensitive elements. Other appropriate filters could be employedas discussed herein-above. The optical filters 34 preferably separatefluorescent emission from the membrane from the excitation energy of theradiation source 18 (e.g., a blue LED). As should be understood based onthe foregoing, most preferably, the complete optical path (e.g., betweenthe waveguide material in the region R and the membranes 14-1 and 14-2,etc.) is refractive index matched so that maximum light capture withminimal internal reflection losses occur.

While FIGS. 27(A) and 27(B) show the excitation source centrally locatedbetween the photosensitive elements 20-1 and 20-2 and the indicator andreference membranes 14-1 and 14-2, the excitation source 18 may beotherwise located, as long as adequate excitation is provided to theindicator and reference membranes 14-1 and 14-2.

As with other embodiments described herein, it is contemplated that theembodiment shown in FIGS. 27(A)-27(B) can be modified in a variety ofways. For instance, a heating element can be provided in embodimentswhere no control channel is used. In addition, as noted, an internalheater can be applied within a variety of sensor constructs in order toreduce condensation on a periphery of a sensor, especially upon sensingmembranes or the like. In addition, other embodiments can include otherknown heating methods. For example, heating coils, wires or the like canbe distributed within the sensor, preferably at least partly proximatethe position of the indicator membranes.

In yet another embodiment of the present invention, the sensor 10 has amatrix that contains indicator molecules that possess one or moremonomeric functions and which are copolymerized with one or morehydrophilic monomers to create a copolymer matrix layer which issuitable for the detection of analytes in aqueous environments. Apolymeric matrix of this type is preferably prepared as described inU.S. patent application Ser. Nos. 09/632,624 and 09/920,627, both ofwhich are incorporated herein by reference. The matrix layer inaccordance with this aspect of the present invention preferably takesthe form of a water-soluble liquid polymeric matrix encased within anadditional biocompatible layer which prohibits the leakage of the liquidpolymeric matrix into the environment. As just one example of a suitableliquid polymeric matrix, U.S. patent application Ser. Nos. 09/632,624and 09/920,627 describe the preparation of water-soluble-copolymericsolutions of MAPTAC [3-(methacryloylamino)propyl]trimethylammoniumchloride and9-[[N-methacryloylaminopropyl-N-(o-boronobenzyl)amino]methyl]anthracene.

As another example, U.S. patent application Ser. No. 09/920,627describes the preparation of water-soluble copolymeric solutions of9-[N-[2-(5,5-dimethylborinan-2-yl)benzyl]-N-[2-(2-methacroyloxy-ethoxy)ethylamino]methyl]-10-[N-[2-(5,5-dimethylborinan-2-yl)benzyl]-N-[2-(2-hydroxyethoxy)ethylamino]methyl]anthraceneand [2-(methacryloxy)ethyl]trimethyl-ammonium chloride (TMAMA).

As is preferred for all indicator matrix constructs, the polymericmatrix of this embodiment is permeable to the analyte(s) to be sensed.

In one embodiment of the present invention, illustrated in FIGS. 29(A)and 29(B), the matrix layer 32 is a water-soluble liquid polymericmatrix that is preferably contained in a recessed portion 31 of thesensor body 12. A cover layer 30 is used to cover and contain thewater-soluable liquid polymeric matrix 32, thereby preventing the escapeand dissolution of that indicator matrix. The cover layer 30 isconstructed to have a suitable size and shape to cover the recessedportion 31 and prevent the escape of the liquid polymer matrix. In apreferred embodiment, the cover layer 30 has a tubular shape having aninside diameter closely matching the outermost diamter of the sensorbody 12. The cover layer 30 is permeable to the analyte(s) to be sensedand is biocompatable.

The cover layer 30 also preferably has a molecular weight cut-off whichis smaller than the nominal molecular weight of the liquid polymericmatrix 32. Cover layer 30 is preferably a dialysis membrane such as, forexample, a cellulose acetate dialysis membrane (MWCO 3500). Othersuitable dialysis membranes may be selected depending upon the molecularweights of the liquid polymeric matrix and analytes of interest.

In a preferred embodiment of the invention illustrated in FIGS. 29(A)and 29(B), the sensor 10 is constructed by sliding or slip-fitting thecover layer 30 over a portion of the annular recess 31 designed tocontain the indicator matrix 32. A predetermined quantity ofconcentrated, dry water-soluble polymer matrix is dispensed into thepocket created by the recess 31 and the cover layer 30. The cover layeris then further slid or slip-fit over the remainder of the annularrecess 31 and into a final position as shown in FIGS. 29(A) and 29(B).The cover layer 30 is then heat sealed or otherwise bonded to the sensorbody 12 in regions 33. The sensor is then immersed in an appropriateaqueous solution, allowing the solution to dissolve the drywater-soluble polymer into an aqueous form of the desired concentration.If necessary, a vacuum may be applied during this step to promoteremoval of any bubbles remaining within annular recess 31.

As indicated above, although specific embodiments of the various aspectsof the invention have been described, numerous modifications andvariations of these embodiments can be made by those in the art. Forexample, aspects of the various embodiments described herein-above canbe applied or interchanged into other embodiments described above aswould be apparent to those in the art based on this disclosure; forinstance, the various embodiments can be adapted to have any one or moreof the indicator molecules described herein-above (or that otherwiseknown) and can be adapted to use any of the control reference methodsdisclosed herein (or that otherwise known). As another example, itshould be understood that various modifications of the electronics,etc., can be made by those in the art based on this disclosure, such as,for example, the various components can be incorporated onto an IC chipor other known modifications or techniques could be employed whilemaintaining one or more aspect of this invention.

In addition, where sensors are powered by and/or communicate with anexternal device, the external device can be made in a variety of formsdepending on circumstances—for example, the external device couldinclude: a wrist mounted enclosure (e.g., similar to a watch) that canbe used in conjunction with a sensor implanted proximate a patient'swrist; a belt mounted or pants mounted enclosure (e.g., similar to acommon “beeper”) that can be used in conjunction with a sensor implantedproximate a patient's hip or waist; a blanket having internalelectronics (e.g., similar to an electric blanket) upon which anindividual can lay down with an implanted device proximate the blanketfor, e.g., ease in obtaining readings while a patient sleeps; anystructure which the sensor can be located near or brought proximate toand/or any structure which can be brought proximate to the sensor; or avariety of other structures and designs.

In addition, as described herein-above, the sensors of the variousembodiments can be used in a variety of applications andenvironments—e.g., in any environment having one or more analyte thatcan be sensed. For example, the various embodiments could be employedwithin various mediums—including, gases (e.g., air and/or any othergases), liquids, solids, combinations thereof, etc. In addition, thevarious embodiments described herein may be readily employed in variousapplications and in various industries, such as in for example: themedical industry (e.g., where sensors may be, for example, insertedinternally into a patient or animal); the food industry (e.g., such aswhere sensors can be inserted into liquids (e.g.: beverages, such asalcoholic beverages, e.g., wine, beer, etc., and non-alcoholicbeverages; and various other liquids); creams; solids; etc.); theconsumer products industry (e.g., where such sensing capabilities areappropriate); and in various other industries as described herein-aboveand as would be apparent based on this disclosure.

Accordingly, it should be understood that a variety of applications,modifications and variations can be made by those in the art within thescope of the following claims.

1. An electro-optical sensing device for detecting the presence of ananalyte in a medium, said sensing device comprising: a. a radiationsource that emits radiation; b. a first and a second photosensitiveelements configured to receive radiation and output an electrical signalin response thereto; c. a first and a second indicator elementspositioned to receive radiation from the radiation source and totransmit radiation to said first and second photosensitive elements,said first and second indicator elements each containing indicatormolecules with an optical characteristic responsive to the presence ofan analyte; and wherein said first indicator element is exposed to anexterior of the device and is responsive to a presence of an analyte ina medium external to the device, and wherein said second indicatorelement is at least partially covered and is insensitive to the presenceof the analyte in the medium external to the device.
 2. The sensingdevice of claim 1, wherein said indicator molecule has an opticalcharacteristic responsive to the presence of oxygen.
 3. The sensingdevice of claim 2, wherein said indicator molecule istris(4,7-diphenyl-1,10-phenanthroline)ruthenium(II) perchlorate.
 4. Thesensing device of claim 1, wherein said first indicator element and saidfirst photosensitive comprise a signal channel, and wherein said secondindicator element and said second photosensitive element comprise areference channel.
 5. The sensing device of claim 4, wherein said signalchannel and said reference channel are incorporated into a chip-likestructure with leads extending therefrom.
 6. The sensing device of claim1, wherein said radiation source is a light emitting diode.
 7. Thesensing device of claim 1, wherein power to the sensing device isprovided from an internal power source.
 8. The sensing device of claim7, wherein said internal power source is a battery.
 9. The sensingdevice of claim 1, wherein power to the sensing device is provided froman external source through an induction circuit formed in the sensingdevice.
 10. The sensing device of claim 1, wherein said indicatormolecule has an optical characteristic responsive to the presence ofglucose.
 11. A method for detecting an analyte of interest in a medium,said method comprising: a. providing an electro-optical sensing devicecontaining a first and a second indicator elements each containingindicator molecules having an optical characteristic responsive to thepresence of an analyte and positioned to receive excitation radiationfrom a radiation source and to transmit resultant radiation to a pair ofphotosensitive elements, and wherein said second indicator elements iscovered by an analyte-impermeable chamber that renders the indicatorelement insensitive to the presence of the analyte in the mediumexternal to the device; b. introducing a medium to contact said firstindicator element; c. activating said radiation source to emit radiationto said first and second indicator elements, d. optically detecting anoptical response of said first and second indicator elements; and e.evaluating said response to determine the presence or concentration ofat least one analyte of interest in the sample, wherein said responsedetected from said second indicator element is used as a reference tocancel variables that affect both said first and second indicatorelements.